Ophthalmic apparatus with corrective meridians having extended tolerance band

ABSTRACT

The embodiments disclosed herein include improved toric lenses and other ophthalmic apparatuses (including, for example, contact lens, intraocular lenses (IOLs), and the like) and associated method for their design and use. In an embodiment, an ophthalmic apparatus (e.g., a toric lens) includes one or more angularly-varying phase members comprising a diffractive or refractive structure, each varying the depths of focus of the apparatus so as to provide an extended tolerance to misalignment of the apparatus when implanted in an eye. That is, the ophthalmic apparatus establishes an extended band of operational meridian over the intended correction meridian.

RELATED APPLICATIONS

This application claims priority to, and the benefit of, U.S.Provisional Appl. No. 62/312,321, filed Mar. 23, 2016; U.S. ProvisionalAppl. No. 62/312,338, filed Mar. 23, 2016; and 62/363,428, filed Jul.18, 2016, each of which is incorporated by reference herein in itsentirety.

TECHNICAL FIELD

This application is directed to lenses for correcting astigmatism,including providing increased tolerance for lens placement duringimplantation.

BACKGROUND

Ophthalmic lenses, such as spectacles, contact lenses and intraocularlenses, may be configured to provide both spherical and cylinder power.The cylinder power of a lens is used to correct the rotationalasymmetric aberration of astigmatism of the cornea or eye, sinceastigmatism cannot be corrected by adjusting the spherical power of thelens alone. Lenses that are configured to correct astigmatism arecommonly referred to as toric lenses. As used herein, a toric lens ischaracterized by a base spherical power (which may be positive,negative, or zero) and a cylinder power that is added to the basespherical power of the lens for correcting astigmatism of the eye.

Toric lenses typically have at least one surface that can be describedby an asymmetric toric shape having two different curvature values intwo orthogonal axes, wherein the toric lens is characterized by a “lowpower meridian” with a constant power equal to the base spherical powerand an orthogonal “high power meridian” with a constant power equal tothe base spherical power plus the cylinder power of the lens.Intraocular lenses, which are used to replace or supplement the naturallens of an eye, may also be configured to have a cylinder power forreducing or correcting astigmatism of the cornea or eye.

Existing toric lenses are designed to correct astigmatic effects byproviding maximum cylindrical power that precisely matches the cylinderaxis. Haptics are used to anchor an intraocular lens to maintain thelenses at a desired orientation once implanted in the eye. However,existing toric lenses themselves are not designed to account formisalignment of the lens that may occur during the surgical implantationof the lens in the eye or to account for unintended post-surgicalmovement of the lens in the eye.

Accordingly, it would be desirable to have intraocular lenses that aretolerant to misalignments.

SUMMARY

The embodiments disclosed herein include improved toric lenses and otherophthalmic apparatuses (including, for example, contact lens,intraocular lenses (IOLs), and the like) and associated method for theirdesign and use. In an embodiment, an ophthalmic apparatus (e.g., a toriclens) includes one or more angularly-varying phase members comprising adiffractive or refractive structure, each varying the depths of focus ofthe apparatus so as to provide an extended tolerance to misalignment ofthe apparatus when implanted in an eye. That is, the ophthalmicapparatus establishes a band of operational meridian over the intendedcorrection meridian.

Several embodiments of ophthalmic apparatus with extended toleranceastigmatism features are disclosed, each configured to establish theextended band of operational meridian.

In an aspect, an ophthalmic apparatus is disclosed. The ophthalmicapparatus includes an angularly-varying phase member configured todirect light, at a first meridian, to a first point of focus, wherein atangular positions nearby to the first meridian, the angularly-varyingphase member is configured to direct light to points of focus nearby tothe first point of focus such that rotational offsets of theangularly-varying phase member from the first meridian directs lightfrom the nearby points of focus to the first point of focus, therebyestablishing an extended band of operational meridian.

In some embodiments, the ophthalmic apparatus includes a multi-zonallens body having a plurality of optical zones, wherein the multi-zonallens body forms the angularly-varying phase member, wherein a heightprofile T1(r, θ) for each meridian θ is defined as: T1(r, θ)=t₁(r)|COS2(θ)|+t₂(r)|SIN 2(θ)|, where t₁(r) and t₂(r) are the added power foreach zone.

In some embodiments, the angularly-varying phase member and otherangularly-varying phase members of the apparatus, collectively, forms abutterfly pattern.

In some embodiments, the multi-zonal lens body includes at least fouroptical zones, the at least four optical zones forming an angularlyvarying efficiency quadric optics (e.g., wherein the angularly varyingefficiency trifocal optics comprises a first angularly varying phasemember, e.g., a first refractive angularly varying phase member, at thefirst meridian; a second angularly varying phase member, e.g., a secondrefractive angularly varying phase member, at a second meridian; a thirdangularly varying phase member, e.g., a third refractive angularlyvarying phase member, at a third meridian; and a fourth refractiveangularly varying phase member, e.g., a fourth refractive angularlyvarying phase member, at a fourth meridian).

In some embodiments, the angularly-varying phase members, collectively,form a butterfly pattern that is expressed as

${{r(\theta)} = \sqrt{2 \cdot n \cdot \frac{{s(\theta)} \cdot \lambda}{A(\theta)}}},$where r(θ) is the contour radius for the given meridian added powerA(θ), wavelength λ, zone number n, and the scaling value s(θ), all atmeridian θ.

In some embodiments, the angularly phase member spans an optical zonedefined by a polynomial-based surface coincident at a plurality ofmeridians having distinct cylinder powers, wherein each of the pluralityof meridians is uniformly arranged on the optical zone for a same givenadded diopter of power up to 1.0D.

In some embodiments, differences among each continuously uniformlydistributed contour line, at a given IOL plane, associated with a givenmeridian of the plurality of meridians is less than about 0.6D(diopters).

In some embodiments, the polynomial-based surface is characterized by aseries of weighted cosine-based functions.

In some embodiments, the angularly phase member spans an optical zonedefined by a freeform-polynomial surface area (e.g., as area having oneor more refractive surfaces) coincident with one or more distinctcylinder powers, wherein the freeform-polynomial surface area is definedas a mathematical expression comprising a combination of one or morepolynomial expressions (e.g., Chebyshev-based polynomial expression,Zernike-based polynomial expression, etc.) each having a distinctcomplex orders.

In some embodiments, at least one of the one or more polynomialexpressions are selected from the group consisting of a Chebyshevpolynomial and a Zernike polynomial.

In some embodiments, the freeform-polynomial surface area establishesthe extended band of operational meridian across a range selected fromthe group consisting of about ±4 degrees, about ±5 degrees, about ±6degrees, about ±7 degrees, about ±8 degrees, about ±9 degrees, about ±10degrees, about ±11 degrees, about ±12 degrees, about ±13, degrees, about±14 degrees, and about ±15 degrees.

In some embodiments, the freeform-polynomial surface area has a secondheight profile T(x,y) (e.g., an extra height profile having anassociated cylinder power) on a first base height profile (e.g., a baseor typical aspheric height profile), the second height profile beingdefined as:T(x,y)=Σ{c(i,j)*cos(i*arccos(t))*cos(j*arccos(t))}where c(i, j) is a coefficient based on i and j, which are each integers(e.g., having a range between 0 and 10), x and y are spatial locationson the freeform-polynomial surface area, and t is a normalized parameterhaving values between −1.0 and 1.0.

In some embodiments, the optical zone is one of a plurality of opticalzones, including a second optical zone, wherein the second optical zoneis defined by a second freeform-polynomial surface region characterizedand defined by a second polynomial, wherein the secondfreeform-polynomial surface area has a third height profile T₂(x,y)(e.g., an extra height profile associated with cylinder power)superimposed on a first height profile (e.g. a base or typical asphericheight profile), the third height profile being defined as:T ₂(x,y)=Σ{c ₂(i ₂ ,j ₂)*cos(i ₂*arccos(t ₂))*cos(j ₂*arccos(t ₂))}

where c₂(i, j) is a coefficient based on i₂ and j₂, which are eachintegers (e.g., ranging between 0 and 10), x and y are spatial locationson the second freeform-polynomial surface area and has values between−1.0 and 1.0, and t₂ is a normalized parameter having values between−1.0 and 1.0 (e.g., associated with the intended correction meridian).

In some embodiments, the first freeform-polynomial surface area and thesecond freeform-polynomial surface area each comprises a monofocal lens,a bifocal lens, a multi-focal lens, or an extended range of vision lens.

In some embodiments, the coefficients c(i, j) or c₂ (i₂, j₂) are afunction of local coordinates that puts accumulated high surfaceamplitude to area of non-functional retinal area.

In some embodiments, the coefficients c(i, j) or c₂(i₂, j₂) are afunction of local coordinates that accounts for irregular corneal shape.

In some embodiments, the angularly-varying phase member is formed of arefractive structure.

In some embodiments, the angularly-varying phase member is formed of adiffractive structure.

In some embodiments, an offset of each meridian of the plurality ofmeridians of about 10 degrees causes a MTF (modulation transferfunction) measure change of less than 10% at 30 cycles per degree (cpd).

In another aspect, an intraocular lens is disclosed, the intraocularlens comprising an angularly-varying phase member configured to directlight, at a first meridian, to a first point of focus, wherein atangular positions nearby to the first meridian, the angularly-varyingphase member is configured to direct light to points of focus nearby tothe first point of focus such that rotational offsets of theangularly-varying phase member from the first meridian directs lightfrom the nearby points of focus to the first point of focus, therebyestablishing an extended band of operational meridian.

In another aspect, an ophthalmic apparatus is disclosed. The ophthalmicapparatus includes a multi-zonal lens body having a plurality of opticalzones, wherein the multi-zonal lens body forms an angularly-varyingphase member having a center at a first meridian, the angularly-varyingphase member, at the center of the first meridian, comprising arefractive structure to direct light to a first point of focus, whereinat angular positions nearby to the first meridian, the refractivestructure directs light to points of focus nearby to the first point offocus such that rotational offsets of the multi-zonal lens body from thecenter of the first meridian directs light from the nearby points offocus to the first point of focus, thereby establishing a band ofoperational meridian for the apparatus to an intended correctionmeridian.

In some embodiments, the refractive structure has a height profile at aface of the ophthalmic apparatus that angularly varies along eachmeridian nearby to the center of the first meridian.

In some embodiments, the height profile of the refractive structureangularly varies in a continuous gradual manner (e.g., in a cosine,sine, or polynomial-based profile).

In some embodiments, the refractive structure angularly varies alongeach meridian nearby to the center of the first meridian up to apre-defined angular position of the apparatus.

In some embodiments, pre-defined angular position is at least about 5degrees from the center of the first meridian.

In some embodiments, the refractive structure varies along each meridianbetween the first meridian and a third meridian that is about 45 degreesoffset to the first meridian and between the first meridian and a fourthmeridian that is about −45 degrees offset to the first meridian.

In some embodiments, the multi-zonal lens body comprises at least threeoptical zones, the at least three optical zones forming an angularlyvarying efficiency trifocal optics (e.g., wherein the angularly varyingefficiency trifocal optics comprises a first angularly varying phasemember, e.g., a first refractive angularly varying phase member, at thefirst meridian; a second angularly varying phase member, e.g., a secondrefractive angularly varying phase member, at a second meridian; and athird angularly varying phase member, e.g., a third refractive angularlyvarying phase member, at a third meridian).

In some embodiments, the multi-zonal lens body comprises at least fouroptical zones, the at least four optical zones forming an angularlyvarying efficiency quadric optics (e.g., wherein the angularly varyingefficiency trifocal optics comprises a first angularly varying phasemember, e.g., a first refractive angularly varying phase member, at thefirst meridian; a second angularly varying phase member, e.g., a secondrefractive angularly varying phase member, at a second meridian; a thirdangularly varying phase member, e.g., a third refractive angularlyvarying phase member, at a third meridian; and a fourth refractiveangularly varying phase member, e.g., a fourth refractive angularlyvarying phase member, at a fourth meridian).

In some embodiments, the multi-zonal lens body forms a secondangularly-varying phase member at a second meridian, wherein the secondmeridian is orthogonal to the first meridian.

In some embodiments, the first angularly-varying phase member and thesecond angularly-varying phase member, collectively, form an angularlyvarying efficiency bifocal optics.

In some embodiments, the second angularly-varying phase member has acenter at the second meridian, the second angularly-varying phase membervarying along each meridian nearby to the center of the second meridiani) between the second meridian and a third meridian that is about 45degrees offset to the second meridian and ii) between the secondmeridian and a fourth meridian that is about −45 degrees offset to thesecond meridian.

In some embodiments, the refractive structure of the first and secondangularly-varying phase members each forms a butterfly pattern.

In some embodiments, the refractive structure of the first and secondangularly-varying phase members, collectively, forms butterfly patternthat is expressed as

${{r(\theta)} = \sqrt{2 \cdot n \cdot \frac{{s(\theta)} \cdot \lambda}{A(\theta)}}},$where r(θ) is the contour radius for the given meridian added powerA(θ), wavelength λ, zone number n, and the scaling value s(θ), all atmeridian θ.

In some embodiments, the angularly-varying phase member at the firstmeridian comprises a monofocal lens.

In some embodiments, the second angularly-varying phase member at thesecond meridian comprises a second monofocal lens.

In some embodiments, each of i) the third meridian located about 45degrees from first meridian and ii) the fourth meridian located about−45 degrees from the first meridian, collectively, form a bifocal lens.

In some embodiments, the height profile T1(r, θ) for each meridian θ isdefined as:T1(r,θ)=t ₁(r)|COS 2(θ)|+t ₂(r)|SIN 2(θ)|where t₁(r) and t₂(r) are the added power for each zone.

In some embodiments, the first angularly-varying phase memberestablishes the extended band of operational meridian across a rangeselected from the group consisting of about ±4 degrees, about ±5degrees, about ±6 degrees, about ±7 degrees, about ±8 degrees, about ±9degrees, about ±10 degrees, about ±11 degrees, about ±12 degrees, about±13, degrees, about ±14 degrees, and about ±15 degrees.

In some embodiments, the ophthalmic apparatus includes a plurality ofalignment markings, including a first set of alignment markings and asecond set of alignment markings, wherein the first set of alignmentmarkings corresponds to the center of the first meridian, and whereinthe second set of alignment markings corresponds to the extended band ofoperational meridian.

In another aspect, a rotationally-tolerant ophthalmic apparatus isdisclosed for correcting astigmatism. The ophthalmic apparatus includesa multi-zonal lens body having a plurality of optical zones configuredto apply cylinder power at an astigmatism meridian of an eye, themulti-zonal lens body forming an angularly-varying phase member having apeak cylinder power centered at an astigmatism correcting meridian, theangularly-varying phase member, at the astigmatism correcting meridian,having a refractive structure configured to direct light to a firstpoint of focus on the retina, and wherein the refractive structure ofthe angularly-varying phase member varies, at each optical zone, alongmeridians nearby to the astigmatism correcting meridian, to direct lightto points of focus nearby to the first point of focus such therefractive structure, when rotationally offset from the peak cylinderpower, directs light from the nearby points of focus to the first pointof focus, thereby establishing a band of operational meridians over theastigmatism meridian.

In another aspect, a rotationally-tolerant ophthalmic apparatus isdisclosed for correcting astigmatism. The ophthalmic apparatus includesan astigmatism correcting meridian corresponding to a peak cylinderpower associated with a correction of an astigmatism, the ophthalmicapparatus having a plurality of exterior alignment markings, including afirst set of alignment markings and a second set of alignment markings,wherein the first set of alignment markings corresponds to theastigmatism correcting meridian, and wherein the second set of alignmentmarkings corresponds to an operational band of the rotationally-tolerantophthalmic apparatus.

In another aspect, an ophthalmic apparatus is disclosed. The ophthalmicapparatus has regions of one or more base spherical powers and one ormore cylinder powers that are added to one or more base spherical powerfor correcting an astigmatism (e.g., an intended astigmatism), theapparatus comprising one or more optical zones, including an opticalzone defined by a polynomial-based surface coincident at a plurality ofmeridians having distinct cylinder powers, wherein light incident to agiven region of a given meridian of each of the plurality of meridians,and respective regions nearby, is directed to a given point of focussuch that the regions nearby to the given region direct light to thegiven point of focus when the given meridian is rotationally offset fromthe given region, thereby establishing an extended band of operation,and wherein each of the plurality of meridians is uniformly arranged onthe optical zone for a same given added diopter of power up to 1.0D.

In some embodiments, differences among each continuously uniformlydistributed contour line, at a given IOL plane, associated with a givenmeridian of the plurality of meridians is less than about 0.6D(diopters).

In some embodiments, the same given added diopter is about 0.5D(diopters).

In some embodiments, the polynomial-based surface establishes theextended band of operation across a range selected from the groupconsisting of about ±5 degrees, about ±6 degrees, about ±7 degrees,about ±8 degrees, about ±9 degrees, about ±10 degrees, about ±11degrees, about ±12 degrees, about ±13, degrees, about ±14 degrees, andabout ±15 degrees.

In some embodiments, the polynomial-based surface is characterized by aseries of weighted cosine-based functions.

In some embodiments, the plurality of meridians include a firstmeridian, a second meridian, and a third meridian, each having theextended band of operation of at least 10 degrees.

In some embodiments, a first center of the first meridian is angularlyspaced about 90 degrees to a second center of the second meridian.

In some embodiments, the optical zone comprises a fourth meridian havingan accumulated high surface amplitude such that the first meridian, thesecond meridian, and the third meridian have the established extendedband of operation.

In some embodiments, the fourth meridian is purposely positioned at anangular position that coincides with a diagnosed limited retinalfunctional area of a patient.

In some embodiments, the polynomial-based surface comprises a refractivesurface.

In some embodiments, the polynomial-based surface comprises adiffractive surface.

In some embodiments, an offset of each meridian of the plurality ofmeridians of about 10 degrees causes a MTF (modulation transferfunction) measure change of less than 10% at 30 cycles per degree (cpd).

In some embodiments, the polynomial-bases surface at a first meridianand at a second meridian comprises a bifocal monofocal lens.

In some embodiments, the polynomial-bases surface at a first meridiancomprises a monofocal lens.

In some embodiments, the polynomial-bases surface at a first meridiancomprises an extended range lens.

In some embodiments, the ophthalmic apparatus includes an accumulatedhigh surface amplitude area disposed at coordinates that coincides withnon-functional or limited functional retinal regions of a given patient.

In another aspect, a rotationally-tolerant ophthalmic apparatus isdisclosed for correcting astigmatism, the ophthalmic apparatuscomprising a multi-zonal lens body having a plurality of optical zonesconfigured to apply cylinder power at an astigmatism meridian of an eye,the multi-zonal lens body forming a angularly-varying phase memberhaving a peak cylinder power centered at an astigmatism correctingmeridian, the angularly-varying phase member at the peak cylinder powerbeing configured to direct light to a first point of focus on theretina, and wherein the angularly-varying phase member varies, at eachoptical zone, along meridians nearby to the astigmatism correctingmeridian to direct light to points of focus nearby to the first point offocus such the multi-zonal lens body, when rotational offset from thepeak cylinder power, directs light from the nearby points of focus tothe first point of focus, thereby establishing a band of operationalmeridians over the astigmatism meridian, and wherein theangularly-varying phase member has a profile that is uniformly spacedfor a same given added diopter of power up to 1.0D (diopters).

In some embodiments, the band of operation is established across a rangeselected from the group consisting of about ±5 degrees, about ±6degrees, about ±7 degrees, about ±8 degrees, about ±9 degrees, about ±10degrees, about ±11 degrees, about ±12 degrees, about ±13, degrees, about±14 degrees, and about ±15 degrees.

In some embodiments, the polynomial-based surface is characterized by aseries of weighted cosine-based function.

In some embodiments, the angularly-varying phase member has a band ofoperation of at least 10 degrees.

In some embodiments, the multi-zonal lens body forms a secondangularly-varying phase member having a second peak cylinder powercentered at a second correcting meridian, the second angularly-varyingphase member at the second peak cylinder power being configured todirect light to a second point of focus on the retina, and wherein thesecond angularly-varying phase member varies, at each optical zone,along meridians nearby to the second correcting meridian to direct lightto points of focus nearby to the second point of focus such themulti-zonal lens body, when rotational offset from the second peakcylinder power, directs light from the nearby points of focus to thesecond point of focus, and wherein the second angularly-varying phasemember has the profile that is uniformly spaced for a same given addeddiopter of power up to 1.0D (diopters).

In some embodiments, the multi-zonal lens body forms a secondangularly-varying phase member having a second peak cylinder powercentered at a second correcting meridian, the second angularly-varyingphase member at the second peak cylinder power being configured todirect light to a second point of focus on the retina, and wherein thesecond angularly-varying phase member varies, at each optical zone,along meridians nearby to the second correcting meridian to direct lightto points of focus nearby to the second point of focus such themulti-zonal lens body, when rotational offset from the second peakcylinder power, directs light from the nearby points of focus to thesecond point of focus, and wherein the second angularly-varying phasemember has a second profile that is uniformly spaced for a same givenadded diopter of power up to 1.0D.

In another aspect, an ophthalmic apparatus is disclosed, the apparatushaving regions of one or more base spherical powers and one or morecylinder powers that are added to the one or more base spherical powerfor correcting an astigmatism (e.g., an intended astigmatism), theapparatus comprising one or more optical zones, including a firstoptical zone defined by a freeform-polynomial surface area (e.g., asarea having one or more refractive surfaces) coincident with one or moredistinct cylinder powers, wherein light incident to a first region ofthe freeform-polynomial surface area, and regions nearby to the firstregion, is directed to a first point of focus such that the regionsnearby to the first region direct light to the first point of focus whenthe first freeform-polynomial surface area is rotationally offset fromthe first region, thereby establishing a band of operational meridianfor the apparatus to an intended correction meridian, and wherein thefreeform-polynomial surface area is defined as a mathematical expressioncomprising a combination of one or more polynomial expressions (e.g.,Chebyshev-based polynomial expression, Zernike-based polynomialexpression, etc.) each having a distinct complex orders.

In some embodiments, at least one of the one or more polynomialexpression is selected from the group consisting of a Chebyshevpolynomial and a Zernike polynomial.

In some embodiments, the freeform-polynomial surface area establishesthe band of operational meridian across a range selected from the groupconsisting of about ±4 degrees, about ±5 degrees, about ±6 degrees,about ±7 degrees, about ±8 degrees, about ±9 degrees, about ±10 degrees,about ±11 degrees, about ±12 degrees, about ±13, degrees, about ±14degrees, and about ±15 degrees.

In some embodiments, the freeform-polynomial surface area has a heightprofile T(x,y) (e.g., an extra height profile having an associatedcylinder power) on a first base height profile (e.g., a base or typicalaspheric height profile), the height profile being defined as:T(x,y)=Σ{c(i,j)*cos(i*arccos(t))*cos(j*arccos(t))}where c(i, j) is a coefficient based on i and j, which are each integers(e.g., having a range between 0 and 10), x and y are spatial locationson the freeform-polynomial surface area, and t is a normalized parameterhaving values between −1.0 and 1.0.

In some embodiments, the freeform-polynomial surface area has the secondheight profile T(x,y) in which i has an order of 0 to at least 6 and jhas an order of 0 to at least 6.

In some embodiments, the freeform-polynomial surface area spans theentire optical face of the apparatus), wherein the ophthalmic apparatuscomprises an optical face (e.g., the portion of the face surface of theophthalmic apparatus that include corrective optical structures) thatincludes the one or more optical zones, the optical face having aboundary defined by a first axis of the face and a second axis of theface (e.g., wherein the first axis is orthogonal to the second axis),and wherein each of the x-spatial locations at value −1.0 and at value1.0 coincides with, or near, the boundary, and each of the y-spatiallocations at value −1.0 and at value 1.0 coincides with, or near, theboundary.

In some embodiments, the ophthalmic apparatus comprises an optical face(e.g., the portion of the face surface of the ophthalmic apparatus thatinclude corrective optical structures) that includes the one or moreoptical zones, the optical face having a boundary defined by a firstaxis of the face and a second axis of the face (e.g., wherein the firstaxis is orthogonal to the second axis), and wherein each of thex-spatial locations at value −1.0 and at value 1.0 is located at a firstradial position along the first axis between a center location of theophthalmic apparatus and the boundary, and wherein each of the y-spatiallocations at value −1.0 and at value 1.0 is located at the first radialposition along the second axis between the center location of theophthalmic apparatus and the boundary.

In some embodiments, the ophthalmic apparatus comprises an optical face(e.g., the portion of the face surface of the ophthalmic apparatus thatinclude corrective optical structures) that includes the one or moreoptical zones, the optical face having a boundary defined by a firstaxis of the face and a second axis of the face (e.g., wherein the firstaxis is orthogonal to the second axis), and wherein each of thex-spatial locations at value −1.0 and at value 1.0 is located at a firstradial position along the first axis between a center location of theophthalmic apparatus and the boundary, and wherein each of the y-spatiallocations at value −1.0 and at value 1.0 is located at a second radialposition along the second axis between the center location of theophthalmic apparatus and the boundary, wherein the first radial positionand the second radial position are different.

In some embodiments, the freeform-polynomial surface area has for eachcontinuously distributed contour line at the IOL plane a difference ofless than about 0.6 Diopters.

In some embodiments, the one or more optical zones includes a secondoptical zone defined by a second freeform-polynomial surface region,wherein the second freeform-polynomial surface area is characterized anddefined by a second polynomial.

In some embodiments, the second freeform polynomial surface area has asecond height profile that varies according to a freeform polynomialselected from the group consisting of a Chebyshev polynomial and aZernike polynomial.

In some embodiments, the one or more optical zones includes a secondoptical zone defined by a second freeform-polynomial surface region,wherein the second freeform-polynomial surface area is characterized anddefined by a second combination of one or more polynomial expressions(e.g., Chebyshev-based polynomial expression, Zernike-based polynomialexpression, etc.) each having a distinct complex orders.

In some embodiments, at least one of the one or more polynomialexpression is selected from the group consisting of a Chebyshevpolynomial and a Zernike polynomial.

In some embodiments, light incident to a second region of the secondfreeform-polynomial surface area, and regions nearby to the secondregion, is directed to a second point of focus such that the regionsnearby to the second region direct light to the second point of focuswhen the second freeform-polynomial surface area is rotationally offsetfrom the second region.

In some embodiments, light incident to a second region of the secondfreeform-polynomial surface area, and regions nearby to the secondregion, is directed to the first point of focus such that the regionsnearby to the second region direct light to the first point of focuswhen the second freeform-polynomial surface area is rotationally offsetfrom the second region (e.g., over the band of operational meridian).

In some embodiments, the second freeform-polynomial surface area has athird height profile T₂(x,y) (e.g., an extra height profile associatedwith cylinder power) superimposed on a first height profile (e.g. a baseor typical aspheric height profile), the third height profile beingdefined as:T ₂(x,y)=Σ{c ₂(i ₂ ,j ₂)*cos(i ₂*arccos(t ₂))*cos(j ₂*arccos(t ₂))}where c₂(i, j) is a coefficient based on i₂ and j₂, which are eachintegers (e.g., ranging between 0 and 10), x and y are spatial locationson the second freeform-polynomial surface area and has values between−1.0 and 1.0, and t₂ is a normalized parameter having values between−1.0 and 1.0 (e.g., associated with the intended correction meridian).

In some embodiments, the first freeform-polynomial surface area comprisea monofocal lens, a bifocal lens, or a multi-focal lens.

In some embodiments, the second freeform-polynomial surface areacomprise a monofocal lens, a bifocal lens, or a multi-focal lens.

In some embodiments, the first freeform-polynomial surface area comprisean extended range of vision lens.

In some embodiments, the second freeform-polynomial surface areacomprise an extended range of vision lens.

In some embodiments, the first freeform-polynomial surface areacomprises refractive surfaces.

In some embodiments, the first freeform-polynomial surface areacomprises diffractive surfaces.

In some embodiments, the coefficients c(i, j) are a function of localcoordinates that puts accumulated high surface amplitude to area ofnon-functional retinal area.

In some embodiments, the coefficients c(i, j) are a function of localcoordinates that accounts for irregular corneal shape.

In another aspect, a method of designing an ophthalmic apparatus (e.g.,the design of FIG. 4) having regions of one or more base sphericalpowers and one or more cylinder powers that are added to the one or morebase spherical power for correcting an astigmatism (e.g., an intendedastigmatism), the method comprising: generating, via a processor, one ormore optical zones, including a first optical zone defined by afreeform-polynomial surface area (e.g., as area having one or morerefractive surfaces) coincident with one or more distinct cylinderpowers, wherein light incident to a first region of thefreeform-polynomial surface area, and regions nearby to the firstregion, is directed to a first point of focus such that the regionsnearby to the first region direct light to the first point of focus whenthe first freeform-polynomial surface area is rotationally offset fromthe first region, thereby establishing a band of operational meridianfor the apparatus to an intended correction meridian, and wherein thefreeform-polynomial surface area is defined as a mathematical expressioncomprising a combination of one or more polynomial expressions (e.g.,Chebyshev-based polynomial expression, Zernike-based polynomialexpression, etc.) each having a distinct complex orders.

It is contemplated that the angularly-varying phase member may be purelyrefractive or a hybrid of diffractive and refractive. It is alsocontemplated that angularly-varying phase members may comprise ofdifferent materials such as a stacking lens, where each layer iscomprised of a different material. It is further contemplated that theangularly-varying phase members may be comprised of a material ormaterials that have a variation in refractive index, a gradient index,or a programmed index, for example liquid crystal which creates therefractive change.

In some embodiments, the angularly-varying phase member establishes theband of operational meridian across a range selected from the groupconsisting of about ±4 degrees, about ±5 degrees, about ±6 degrees,about ±7 degrees, about ±8 degrees, about ±9 degrees, about ±10 degrees,about ±11 degrees, about ±12 degrees, about ±13, degrees, about ±14degrees, and about ±15 degrees.

In another aspect, a rotationally-tolerant ophthalmic apparatus (e.g.,toric intraocular lens) having an established band of operationmeridians (e.g., at least about ±4 degrees or more) for placement overan intended astigmatism meridian is disclosed. The ophthalmic apparatusincludes a multi-zonal lens body having a plurality of optical zones,where the multi-zonal lens body forms the angularly-varying phasemember. The angularly-varying phase member has a center at anastigmatism correction meridian that directs light to a first point offocus (e.g., on the retina). At angular positions nearby to theastigmatism correction meridian, the portion of the angularly-varyingphase member at such angular positions directs light to points of focusof varying depths and nearby to the first point of focus such thatrotational offsets of the multi-zonal lens body from the center of theastigmatism correction meridian directs light from the nearby points offocus to the first point of focus.

In another aspect, a rotationally-tolerant ophthalmic apparatus forcorrecting astigmatism is disclosed. The ophthalmic apparatus includesan astigmatism correcting meridian that corresponds to a peak cylinderpower associated with a correction of an astigmatism. Therotationally-tolerant ophthalmic apparatus may include a plurality ofexterior alignment markings, including a first set of alignment markingsand a second set of alignment markings. The first set of alignmentmarkings corresponds to the astigmatism correcting meridian, and thesecond set of alignment markings corresponds to an operation band of therotationally-tolerant ophthalmic apparatus.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the present invention may be better understood from thefollowing detailed description when read in conjunction with theaccompanying drawings. Such embodiments, which are for illustrativepurposes only, depict novel and non-obvious aspects of the invention.The drawings include the following figures:

FIGS. 1A and 1B are diagrams of an exemplary ophthalmic apparatus (e.g.,an intraocular toric lens) that includes angularly-varying phase members(reflective, diffractive, or both) that each provides an extendedrotational tolerance of the apparatus in accordance with an illustrativeembodiment.

FIGS. 2A, 2B, 2C, 2D, 2E, and 2F, each illustrates a plurality ofexemplary height profiles of the anterior or posterior face of theophthalmic apparatus of FIGS. 1A-1B in accordance with an illustrativeembodiment.

FIG. 3 is a schematic drawing of a top view of a human eye, in which thenatural lens of the eye has been removed and replaced with an ophthalmicapparatus that includes angularly-varying phase members in accordancewith an illustrative embodiment.

FIGS. 4A, 4B, 4C, and 4D are schematic diagrams of exemplary ophthalmicapparatuses that include either refractive or diffractiveangularly-varying phase members, in accordance with an illustrativeembodiment.

FIGS. 5A and 5B are plots illustrating performance of a conventionaltoric lens designed to apply maximum cylinder power at a correctivemeridian when subjected to rotational misalignment.

FIGS. 6A and 6B show plots of off-axis performances of an exemplaryophthalmic apparatus (diffractive or refractive) that includesangularly-varying phase members in accordance with an illustrativeembodiment.

FIGS. 7A and 7B are diagrams of an exemplary ophthalmic apparatus thatincludes angularly-varying phase members in accordance with anotherillustrative embodiment.

FIGS. 8 and 9 are diagrams illustrating height profiles of exemplaryophthalmic apparatuses of FIGS. 1A-1B and 7A-7B in accordance with theillustrative embodiments.

FIG. 10 is a diagram of an exemplary multi-focal lens ophthalmicapparatus that includes angularly-varying phase members in accordancewith another illustrative embodiment.

FIG. 11 is a diagram illustrating the multi-focal lens ophthalmicapparatus of FIG. 10 configured as a bifocal lens in accordance withanother illustrative embodiment.

FIG. 12 is a diagram illustrating the multi-focal lens ophthalmicapparatus of FIG. 10 configured as a tri-focal lens in accordance withanother illustrative embodiment.

FIG. 13 is a diagram of an exemplary ophthalmic apparatus that includesangularly-varying phase members (refractive, diffractive, or both) inaccordance with another illustrative embodiment.

FIG. 14 is a table of the ophthalmic apparatus of FIG. 13 configured asa tri-focal lens in accordance with another illustrative embodiment.

FIGS. 15A and 15B are diagrams of an exemplary ophthalmic apparatus thatincludes angularly-varying phase members with asymmetric height profilesin accordance with another illustrative embodiment.

FIGS. 16A, 16B, and 16C, each illustrates a plurality of exemplaryheight profiles of the ophthalmic apparatus of FIGS. 15A-15B inaccordance with an illustrative embodiment.

FIGS. 17A and 17B are diagrams of an exemplary ophthalmic apparatus thatincludes angularly-varying phase members and a symmetric height profilein accordance with another illustrative embodiment.

FIGS. 18A, 18B, and 18C, each illustrates a plurality of exemplaryheight profiles of the anterior or posterior face of the ophthalmicapparatus of FIGS. 17A-17B in accordance with an illustrativeembodiment.

FIGS. 19A and 19B are diagrams of an exemplary ophthalmic apparatus thatincludes refractive angularly-varying phase members in accordance withanother illustrative embodiment.

FIGS. 20A, 20B, 20C, 20D, and 20E illustrate a plurality of exemplaryheight profiles of the anterior or posterior face of the ophthalmicapparatus of FIGS. 19A-19B, in accordance with an illustrativeembodiment.

FIGS. 21A, 21B, and 21C are diagrams illustrating an exemplaryophthalmic apparatus that includes refractive angularly-varying phasemembers, in accordance with another illustrative embodiment.

FIGS. 22A and 22B are diagrams illustrating a top and bottom view of anophthalmic apparatus of FIGS. 15A-15B with extended tolerance bandmarkers in accordance with an illustrative embodiment.

FIG. 23 is diagram of a method to generate, via a processor, the surfacewith the angularly-varying phase members, in accordance with anillustrative embodiment.

FIG. 24 is a diagram of an example freeform-polynomial surface area thatprovides extended rotational tolerance, in accordance with anillustrative embodiment.

FIG. 25 illustrates an example operation of the freeform-polynomialsurface area of FIG. 24 when subjected to misalignment, in accordancewith an illustrative embodiment.

FIG. 26 shows a combined cylinder map generated from the combination ofthe IOL cylindrical power (provided, in part, via thefreeform-polynomial surface) combined with the corneal cylindrical powerthrough meridians.

FIGS. 27A and 27B each shows calculated MTF values as spatialfrequencies of an exemplified IOL in a physiological eye model withastigmatic cornea in different cylindrical axis misalignment (CAM)situations between the cornea and the IOL for an iris pupil.

FIG. 28A shows a diagram of a freeform-polynomial surface area (e.g.,the second or third height profile) of a second optical zone thatsymmetrically spans part of the optical face of the apparatus, inaccordance with an illustrative embodiment.

FIG. 28B shows a diagram of a freeform-polynomial surface area (e.g.,the second or third height profile) of a second optical zone thatsymmetrically spans part of the optical face of the apparatus, inaccordance with an illustrative embodiment.

FIG. 29 is a diagram of cylindrical map of a polynomial surface that isuniformly arranged over a plurality of meridians that provides extendedrotational tolerance, in accordance with an illustrative embodiment.

FIG. 30 is a diagram of the ETA polynomial surface of FIG. 29 shown withthe plurality of uniformly arranged meridians, in accordance with anillustrative embodiment.

FIG. 31 is a profile of the polynomial surface of FIG. 29 with theplurality of uniformly arranged meridians, in accordance with anillustrative embodiment.

FIG. 32 illustrates an example operation of the polynomial surface ofFIG. 29 when subjected to misalignment, in accordance with anillustrative embodiment.

FIG. 33 shows a combined cylinder map generated from the combination ofthe IOL cylindrical power (provided, in part, via the polynomialsurface) combined with the corneal cylindrical power through meridians.

FIG. 34 shows the combined cylinder map of FIG. 33 with the meridiansshown in FIG. 30 superimposed thereon.

FIGS. 35A and 35B each shows calculated MTF values as spatialfrequencies of an exemplified IOL 100 in a physiological eye model withastigmatic cornea in different cylindrical axis misalignment (CAM)situations between the cornea and the IOL for an iris pupil.

FIG. 36 is a surface SAG map of the polynomial surface 2902 of FIG. 29,in accordance with an illustrative embodiment.

FIG. 37 is a diagram of an example computing device configured togenerate the surface with the angularly-varying phase members.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

Each and every feature described herein, and each and every combinationof two or more of such features, is included within the scope of thepresent invention provided that the features included in such acombination are not mutually inconsistent.

Embodiments of the present invention are generally directed to toriclenses or surface shapes, and/or related methods and systems forfabrication and use thereof. Toric lenses according to embodiments ofthe present disclosure find particular use in or on the eyes of human oranimal subjects. Embodiments of the present disclosure are illustratedbelow with particular reference to intraocular lenses; however, othertypes of lenses fall within the scope of the present disclosure.Embodiments of the present disclosure provide improved ophthalmic lens(including, for example, contact lenses, and intraocular lenses, corneallenses and the like) and include monofocal refractive lenses, monofocaldiffractive lenses, bifocal refractive lenses, bifocal diffractivelenses, and multifocal refractive lenses, multifocal diffractive lenses.

As used herein, the term “refractive optical power” or “refractivepower” means optical power produced by the refraction of light as itinteracts with a surface, lens, or optic. As used herein, the term“diffractive optical power” or “diffractive power” means optical powerresulting from the diffraction of light as it interacts with a surface,lens, or optic.

As used herein, the term “optical power” means the ability of a lens oroptics, or portion thereof, to converge or diverge light to provide afocus (real or virtual), and is commonly specified in units ofreciprocal meters (m⁻¹) or Diopters (D). When used in reference to anintraocular lens, the term “optical power” means the optical power ofthe intraocular lens when disposed within a media having a refractiveindex of 1.336 (generally considered to be the refractive index of theaqueous and vitreous humors of the human eye), unless otherwisespecified. Except where noted otherwise, the optical power of a lens oroptic is from a reference plane associated with the lens or optic (e.g.,a principal plane of an optic). As used herein, a cylinder power refersto the power required to correct for astigmatism resulting fromimperfections of the cornea and/or surgically induced astigmatism.

As used herein, the terms “about” or “approximately”, when used inreference to a Diopter value of an optical power, mean within plus orminus 0.25 Diopter of the referenced optical power(s). As used herein,the terms “about” or “approximately”, when used in reference to apercentage (%), mean within plus or minus one percent (±1%). As usedherein, the terms “about” or “approximately”, when used in reference toa linear dimension (e.g., length, width, thickness, distance, etc.) meanwithin plus or minus one percent (1%) of the value of the referencedlinear dimension.

FIGS. 1A and 1B are diagrams of an exemplary ophthalmic apparatus 100(e.g., an intraocular toric lens) that includes angularly-varying phasemembers 102 (refractive, diffractive, or both) configured to provideextended rotational tolerance in accordance with an illustrativeembodiment.

The angularly-varying phase members have a center structure that appliescylinder power at a corrective meridian (e.g., the high power meridian).In FIGS. 1A and 1B, the corrective meridian is shown at Θ=0° and Θ=180°with the center structure being disposed at such Θ positions. Off-centerstructures of the angularly-varying phase members extend from the centerstructure in a gradually varying manner to apply cylinder power to aband of meridians surrounding the corrective meridian enabling theophthalmic apparatus to operate off-axis (or off-meridian) to thecorrective meridian (e.g., the astigmatism meridian). As shown in FIG.1A, the off-center structures extends, at least, from Θ=0° to Θ=10° andΘ=−10° to facilitate off-axis operation (from Θ=0°) up to ±10°. Theoff-center structures may extend from Θ=0° to Θ=90° and Θ=−90°. Thesemeridians may be referred to as a dynamic meridian.

Although the operational boundaries of the angularly varying phasemembers are shown to be at about ±10°, it is contemplated that otherangular values may be used, as are discussed herein. In addition, insome embodiments, it is also contemplated that operational boundariesmay be symmetrical or asymmetrical. For example, in certain embodiments,the operational boundaries may be skewed to one rotation, e.g., between+9° and −11° or, e.g., between +11° and −9°.

The angularly-varying phase members, in some embodiments, include anoptimized combination of angularly and zonally diffractive (orrefractive) phase structure located at each meridian to vary theextended depth of focus to a plurality of nearby focus points. Lightdirected to such nearby focus points are thus directed to the desiredfocus point when the ophthalmic apparatus is subjected to a rotationaloffset from a primary intended axis of alignment, thereby extending therotational tolerance of the apparatus to an extended tolerance band.This may also be referred to as “extended tolerance astigmatism band” or“extended misalignment band.” Remarkably, this extended toleranceastigmatism band delivers cylinder power to correct for the astigmatismfor a range of meridians (e.g., up to ±10° or more as shown in FIGS. 1Aand 1B), thereby eliminating any need for additional corrective measures(e.g., supplemental corrective devices or another surgical intervention)when the implanted ophthalmic apparatus is not perfectly aligned to thedesired astigmatism meridian in the eye.

Put another way, the angularly-varying phase members facilitate anextended band of the corrective meridian that has minimal, and/orclinically acceptable, degradation of the visual acuity and modulationtransfer function when the ophthalmic apparatus is subjected torotational misalignment between the astigmatic axis and a center axis ofthe corrective meridian.

In some embodiments, an exemplified toric IOL includes dynamic meridianor angularly varying efficiency quadric optics. In another embodiment,an exemplified toric IOL includes dynamic meridian or angularly varyingefficiency trifocal optics. In another embodiment, an exemplified toricIOL includes double dynamic meridian or angularly varying efficiencybifocal optics. In another embodiment, the bifocal or trifocal featuremay be disposed on one optical surface or on both optical surfaces of asingle optical lens or on any surfaces of a multiple optical elementsworking together as a system.

Referring still to FIGS. 1A and 1B, an embodiment of theangularly-varying phase members 102 is shown. In this embodiment, theangularly-varying phase members 102 are formed in multiple-zones (shownas zones 120 a, 120 b, 120 c), each forming a spatially-varying“butterfly” shaped structure centered around the optical axis 106. Themultiple-zone structure (120 a, 120 b, and 120 c), and angularly-varyingphase members 102 therein, form a first “high power meridian” (e.g.,having a constant power equal to the base spherical power plus acylinder power of the lens) at a first meridian (e.g., axis 110 shown asΘ=0° and Θ=180°) that corresponds to an axis of the eye to apply acorrection. The first corrective meridian 110 focuses light that passestherethrough to a first foci (i.e., point of focus) and is intended toalign with the astigmatic axis of the eye. At nearby meridians (e.g.,−10°, −9°, −8°, −7°, −6°, −5°, −4°, −3°, −2°, −1°, 1°, 2°, 3°, 4°, 5°,6°, 7°, 8°, 9°, and 10°), the angularly-varying phase members 102 focuslight that passes therethrough to a plurality of foci near the firstfoci. The angularly-varying phase members 102 vary from between thefirst meridian (Θ=0°) and another meridian located about 10 degrees fromthe first meridian (e.g., axis 114 shown as Θ=10°).

FIGS. 1A and 1B illustrate the exemplary ophthalmic apparatus 100 havinga diffractive surface 120. A diffractive surface comprises multipleechelette elements. In some embodiments, an intraocular lens, which hasa diffractive grating covering its entire surface, has between 15 and32, or more echelette elements. In some embodiments, the diffractivegrating includes more than 32 echelette elements. As shown in FIGS. 1Aand 1B, multiple echelette elements cover each region, or if there isone echelette element, or the echelette spans only a portion of theregion, then a refractive area will cover the rest of the region. Thoughshown here as a diffractive surface, the angularly varying phase membersare later illustrated as a refractive surface, as later discussedherein.

As shown in FIGS. 1A and 1B, both the heights (i.e., thicknesses) of thelens and the spatial sizes, at each zone, vary among the different axesto form the angularly-varying phase member 102. To illustrate thisstructure, both a first height profile 116 of the lens along the firstcorrective meridian (e.g., at Θ=0°) and a second height profile 118 ofthe lens along a lower power meridian (i.e., at axis 114 shown as Θ=10°)are presented at plots 108 a and 108 b, respectively, for each of FIGS.1A and 1B. The height profile of the lens varies at each axis as thefirst height profile 116 gradually transitions (e.g., as shown by thecurved profile 122) into the second height profile 118. The first andsecond height profiles 116 and 118 are illustrated relative to oneanother in a simplified format. It should be appreciated that there maybe multiple echelette elements (i.e., diffractive structures) in each ofthe multiple zone structures, surrounded by a refractive region.Alternatively, rather than relying on diffraction, one or more of themultiple zone structures may have only refraction surfaces to varypower.

It should also be appreciated that the height profiles herein areillustrated in a simplified form (e.g., as a straight line). The heightprofiles for each zone may form other surfaces—such as refractive,diffractive—or have other shapes—such convex, concave, or combinationsthereof. The profiles may be added to, or incorporated into, a base lensas, for example, shown in FIGS. 4A, 4B, 4C, and 4D. FIGS. 4A, 4B, 4C,and 4D are schematic diagrams of exemplary ophthalmic apparatuses thatinclude either refractive or diffractive angularly-varying phasemembers, in accordance with an illustrative embodiment.

Referring still to FIGS. 1A and 1B, the multiple-zone structure (e.g.,104 a, 104 b, and 104 c), and angularly-varying phase members 126therein, form a second “high power meridian” 112 (i.e., axis 112 shownas Θ=90°) which is orthogonal to the first corrective meridian 110. Thesecond corrective meridian 112 includes a second angularly varying phasestructure 126. In some embodiments, the second angularly varying phasestructure focuses light to a second set of foci (e.g., as part of amulti-focal lens configuration).

FIGS. 2A, 2B, 2C, 2D, 2E, and 2F, each illustrates a plurality of heightprofiles of the angularly-varying phase member 102 of FIGS. 1A and 1Bbetween the first high power meridian (at Θ=0°) and the operational edgeof the angularly varying phase members in accordance with anillustrative embodiment. In FIG. 2B, representative height profiles (ofan echelette element) at Θ=0° (202); Θ=2° (204); Θ=4° (206); Θ=6° (208);Θ=8° (210); and Θ=10° (212) (also shown in FIG. 2A) are provided ascross-sections of the echelette elements at the different meridiansshown in FIG. 2A. As shown, the height profiles at axes nearby to thefirst high power meridian (e.g., between ±10°) have a similar shape, asthe first high power meridian. The height profile varies in a continuousgradual manner (e.g., having a sine and cosine relationship) along theradial direction (e.g., at different radial values) and along theangular direction (e.g., at different angular positions). The varying ofthe angular position and of the radial position, e.g., between Θ=0° andΘ=10° and between Θ=0° and Θ=−10° forms the angularly varying phasemember. This can also be observed in FIGS. 2B and 2C. In FIGS. 2B and2C, the edge of an echelette element of the height profile of theangularly-varying phase member at Θ=2° (204) is shown to vary moreabruptly in relation to the center meridian at Θ=0° (202). The abrupttransition in the edge position is shown to transition more slowly atΘ=4° (206), and even more slowly at Θ=6° (208); then Θ=8° (210); andthen Θ=10° (212). In contrast, the height profile transitions moreslowly near the center meridian at Θ=0° and then more sharply at theedge. This transition may be described as a cosine-based or sine-basedfunction, a polynomial function, or a function derived from acombination thereof.

FIG. 2C illustrates a height profiles (near the optical axis and betweenthe operational boundaries of the angularly varying phase member 102) atΘ=0° (202); Θ=2° and −2° (204); Θ=4° and −4° (206); Θ=6° and −6° (208);Θ=8° and −8° (210); and Θ=10° and −10° (212) superimposed next to oneanother. This variation of the height profile along the radial axisprovides a lens region that focuses light at the desired foci and otherfoci nearby. To this end, radial offset (i.e., misalignment) of theophthalmic apparatus from the center axis of a desired correctivemeridian results in its nearby regions focusing the light to the desiredfoci. This effect is further illustrated in FIG. 3.

In FIGS. 2D, 2E, and 2F, example height profiles of the lens surfacebetween Θ=0° and Θ=45° are shown. As shown in FIGS. 2E and 2F, theheight profiles of the angularly varying phase member vary as acosine-based or sine-based function. In some embodiments, the heightprofiles of the lens surface between Θ=45° and Θ=90° are mirrored atΘ=45° to the lens surface between Θ=0° and Θ=45°.

FIG. 3 is a schematic drawing of a top view of a human eye 302, in whichthe natural lens of the eye 302 has been removed and replaced with anintraocular lens 100 (shown in simplified form in the upper portion ofFIG. 3 and in greater detail in the lower portion of FIG. 3). Lightenters from the left of FIG. 3, and passes through the cornea 304, theanterior chamber 306, the iris 308, and enters the capsular bag 310.Prior to surgery, the natural lens occupies essentially the entireinterior of the capsular bag 310. After surgery, the capsular bag 310houses the intraocular lens 100, in addition to a fluid that occupiesthe remaining volume and equalizes the pressure in the eye.

After passing through the intraocular lens, light exits the posteriorwall 312 of the capsular bag 310, passes through the posterior chamber328, and strikes the retina 330, which detects the light and converts itto a signal transmitted through the optic nerve 332 to the brain. Theintraocular lens 100 comprises an optic 324 and may include one or morehaptics 326 that are attached to the optic 324 and may serve to centerthe optic 324 in the eye and/or couple the optic 324 to the capsular bag310 and/or zonular fibers 320 of the eye.

The optic 324 has an anterior surface 334 and a posterior surface 336,each having a particular shape that contributes to the refractive ordiffractive properties of the lens. Either or both of these lenssurfaces may optionally have an element made integral with or attachedto the surfaces. FIGS. 4A, 4B, 4C, and 4D are schematic diagrams ofexemplary ophthalmic apparatuses that include either refractive ordiffractive angularly-varying phase members, in accordance with anillustrative embodiment. Specifically, FIGS. 4A and 4B show examples ofdiffractive lenses, and FIGS. 4C and 4D show examples of refractivelenses. The diffractive lenses or refractive lenses includes theangularly varying phase members as described herein. The refractiveand/or diffractive elements on the anterior and/or posterior surfaces,in some embodiments, have anamorphic or toric features that can generateastigmatism to offset the astigmatism from a particular cornea in aneye.

Referring still to FIG. 3, the intraocular lens 100 includesangularly-varying phase members (reflective, diffractive, or both) thatfocus at a plurality of focus points that are offset radially to oneanother so as to provide an extended tolerance to misalignments of thelens 100 when implanted into the eye 302. That is, when the center axisof a corrective meridian is exactly matched to the desired astigmaticaxis, only a first portion of the cylinder axis is focused at thedesired point of focus (338) (e.g., at the retina) while second portionsof the cylinder axis focuses at other points (340) nearby that areradially offset to the desired point of focus (338). To this end, whenthe primary axis of the astigmatism of the intraocular lens isrotationally offset (shown as arrow 342) with the astigmatism of theeye, the second portion of the cylinder axis focuses the light to thedesired point of focus.

Artificial lenses (e.g., contact lenses or artificial intraocularlenses) can correct for certain visual impairments such as an inabilityof the natural lens to focus at near, intermediate or far distances;and/or astigmatism. Intraocular toric lenses have the potential forcorrecting astigmatism while also correcting for other visionimpairments such as cataract, presbyopia, etc. However, in somepatients, implanted intraocular toric lenses may not adequately correctastigmatism due to rotational misalignment of the corrective meridian ofthe lenses with the astigmatic meridian. In some patients following thesurgical implant of the toric lenses, the corrective meridian of theimplanted toric lenses can be rotationally misaligned to the astigmaticmeridian, in some instances, by as much as 10 degrees. However, toriclenses that are designed to provide maximum correction (e.g., 1D to 9D)at the astigmatic meridian are subject to significant reduction ineffectiveness of the correction due to any misalignment from thecorrective meridian. In certain designs, it is observed that if thecylindrical power axis were mismatched by 1 degree, there would be about3 percent reduction of the effectiveness of the correction. Thedegradation increases with the degree of misalignment. If there were a10-degree misalignment, there would be about 35% reduction of theeffectiveness of the correction. This effect is illustrated in FIG. 4discussed below.

FIGS. 5A and 5B include plots that illustrated the above-discusseddegraded performance of conventional toric lens when subjected torotational misalignments. This conventional toric lens is configured toprovide 6.00 Diopters cylinder powers at the IOL plane, 4.11 Diopterscylinder power at the corneal plane, and a corneal astigmatismcorrection range (i.e., preoperative corneal astigmatism to predictedeffects) between 4.00 and 4.75 Diopters.

Referring to FIG. 5A, a plot of the undesired meridian power (alsoreferred to as a residual meridian power (“OC”)) (shown along they-axis) added due to the rotational misalignments (shown along thex-axis) of the toric IOL is shown, including the residual powers for i)a negative 10-degree misalignment (shown as line 502), ii) a 0-degreemisalignment (shown as line 504), and iii) a positive 10-degreemisalignment (shown as line 506). As shown, the undesired added meridianpower varies between a maximum of ±0.75 Diopters at around the 45-degreemeridian angle (shown as 508) and at about the 135-degree meridian angle(shown as 510). Notably, this undesired added meridian power is outsidethe tolerance of a healthy human eye, which can tolerant undesiredeffects up to about 0.4 Diopters (e.g., at the cornea plane) for normalvisual acuity (i.e., “20/20 vision”). Because the undesired effectsexceeds the astigmatism tolerance of the human eye, correctiveprescription glasses, or further surgical operation to correct theimplant misalignment, may be necessary to mitigate the effects of themisalignment of such toric IOLs.

This undesired meridian power may be expressed as Equation 1 below.

$\begin{matrix}{{OC} = {2\mspace{11mu}\sin\mspace{11mu}\alpha*\frac{c}{2}0.7\mspace{11mu}\cos\mspace{11mu}\left( {2\left( {\theta + 90 + \frac{\alpha}{2}} \right)} \right)}} & \left( {{Equation}\mspace{14mu} 1} \right)\end{matrix}$

As shown in Equation 1, θ is the correction meridian (also referred toas the cylindrical power axis) (in degrees); C is the astigmatic power(at the IOL plane) to be corrected at meridian θ (in Diopters); and a isthe magnitude of rotational misalignment of the cylindrical power axisto the astigmatic axis (in degrees).

FIG. 5B shows a plot illustrating the tolerance of a toric IOL tomisalignment (shown in the y-axis) and a corresponding cylindrical powerthat may be applied (shown in the x-axis) for each misalignment to notexceed the astigmatism tolerance of the human eye (i.e., degrade theoverall visual acuity). The tolerance to misalignment may be calculatedas

${\alpha } \leq \sin^{{- 1}\frac{0.4}{\frac{2}{\frac{C}{0.7}}}}$where α is the magnitude of rotational misalignment (in degrees). Thecalculation may be reduced to

${\alpha } \leq {\sin^{{- 1}\frac{0.29}{C}}.}$As shown, for a misalignment of 5 degrees, which is routinely observedin IOL implantations, the correction effectiveness of such IOL implantscan only be maintained for a toric IOL with 3.75 Diopters or less. Thatis, a toric IOL having cylinder power above 3.75 Diopters would exhibitdegraded visual acuity due to the residual power exceeding theastigmatism tolerance of a human eye. This effect is worsen with furtherdegrees of misalignment. For example, at about 10 degrees, theeffectiveness of a toric IOL is greatly reduced where only 1.5 Diopterscylinder power or less can be applied so as to not detrimentally effectthe visual acuity. Given that cylinder power of convention toric IOLsmay range between 1.00 Diopters and 9.00 Diopters, these toric IOLs arereduced in effectiveness post-operation due to the misalignments ofcylinder axis.

Each of FIGS. 6A and 6B shows plots illustrating modular transferfunctions (MTFs) in white light for two toric IOLs (shown as 602 a and602 b) each configured with angularly-varying phased members whensubjected to off-axis rotations. FIG. 6A illustrates the performance fora refractive toric IOL, and FIG. 6B illustrates performance for adiffractive toric IOL.

Remarkably, the cylinder power of the lens configured with angularlyvarying phase members provides an extended tolerance of misalignment upto 10 degrees, and more, of off-axis rotation. As shown in FIGS. 6A and6B, the modulation transfer function (MTF) is maintained across theextended range of alignment for a lens configured with the angularlyvarying phase members. In contrast, at certain degrees of misalignment,the MTF of a toric IOL (shown as lines 604 a and 604 b) without theangularly varying phase member is near zero. For example, as shown inFIG. 6A, the MTF at about 3.5 degrees misalignment for a conventionaltoric lens is near zero. MTF is a modulation of the amplitude and phasefunctions of an image formed by the white light on a specified plane,e.g., the retina of the human eye, and characterizes the sensitivity ofthe lens.

Referring still to FIGS. 6A and 6B, an ophthalmic apparatus thatincludes angularly varying phase members has a lower maximum cylinderrange (as compared to lens without such structure). Rather, theangularly varying phase members apply the cylinder power to a bandsurrounding the corrective meridian, thereby providing a continuous bandthat makes the lens may tolerant due to misalignment. As shown, in thisembodiment, the sensitivity of the ophthalmic apparatus with theangularly varying phase members is less by 20% as compared to a lenswithout the angularly varying phase members. And, at 10 degrees ofmisalignment (or off-axis operation) from the targeted corrective axis,the modulation transfer function (MTF) degradation for the ophthalmicapparatus configured with the angularly varying phase member is stillacceptable. In this example, the ophthalmic apparatus configured withthe angularly varying phase members is configured as a monofocal toriclens with 4.0 Diopters cylindrical power. Here, the MTF is at 100 lp/-mmand has a spatial frequency equivalent to 30 c/degree for an emmetropiaeye with 20/20 visual acuity. The performance of the toric IOL with theangularly varying phase member at 5 degrees off-meridian (e.g., line 602a) has comparable MTF performance to a similar toric IOL without theangularly varying phase structure at 2 degrees of misalignment (e.g.,line 604 a).

FIGS. 7A and 7B are diagrams of an ophthalmic apparatus 100 (e.g., anintraocular toric lens) that includes angularly-varying phase members102 (reflective, diffractive, or both) that disperse light therethroughto a plurality of foci that are offset radially to one another so as toprovide an extended tolerance to misalignments of the lens 100 whenimplanted in an eye in accordance with another illustrative embodiment.As shown in FIGS. 7A-7B, the apparatus 100 has an asymmetric heightprofile 702 in which the maximum height of the face of the apparatusdiffers between the different zones. To demonstrate the asymmetricheight profile 702, representative echelette in zones 120 b and 120 c ofan example refractive surface is shown. In zone 120 b, the height of arepresentative echelette 704 is shown to be greater than the height of arepresentative echelette 706 in zone 120 c.

In some embodiments, the asymmetric height profile 702 may be configuredto direct light to a plurality foci. For example, the apparatus 100 withthe asymmetric height profile 702 may be used for as a trifocal lens. Inother embodiments, the apparatus with the asymmetric height profile 702is used for a quad-focal lens. In some embodiments, the apparatus 100with the asymmetric height profile 702 is used for a double bi-focallens. In some embodiments, the apparatus 100 with the asymmetric heightprofile 702 is used for a mono-focal lens. In some embodiments, theapparatus 100 with the asymmetric height profile 702 is used for acombined bi-focal and tri-focal lens. In some embodiments, the apparatus100 with the asymmetric height profile 702 is used for an anteriorbifocal and a posterior tri-focal lens. In some embodiments, theapparatus 100 with the asymmetric height profile 702 is used for aposterior bifocal and an anterior tri-focal lens.

FIGS. 8 and 9 illustrate a plurality of height profiles of theangularly-varying phase members 102 of the lens in accordance withvarious illustrative embodiments. As shown in FIG. 8, the height profileis symmetric at each meridian in that the maximum height (shown as 802,804, and 806) at the face of the lens are the same. As shown in FIG. 9,the height profile is asymmetric in that the maximum height at the faceof the lens are different.

FIG. 10 illustrates an example multi-focal intraocular lens 1000configured with angularly varying phase members in accordance with anillustrative embodiment. As shown, the lens 1000 provides a mono-focalat corrective meridian Θ=0° and 180°. In addition, the lens 1000provides a second mono-focal at corrective meridian Θ=90° and −90°. Inaddition, the lens 1000 provides a first bi-focal at Θ=−45° and 135°. Inaddition, the lens 1000 provides a second bi-focal at Θ=45° and −135°.In some embodiments, the lens is refractive. In other embodiments, thelens is diffractive.

With the angularly varying phase members, images at all meridians (Θ=0°,Θ=45°, Θ=90°, Θ=135°, Θ=180°, Θ=−135°, Θ=−90°, and Θ=−45°) reach a 20/20“uncorrected distance visual acuity” (UDVA). FIGS. 11 and 12 arediagrams illustrating added cylindrical power, from the angularlyvarying phase members, in the radial and angular position in accordancewith the illustrative embodiments.

FIG. 11 illustrates added cylinder power by the angularly varying phasemembers for a multi-focal intraocular lens configured as a bifocal. Asshown in FIG. 11, for a given cylindrical power (e.g., 6.0 Diopters),the angularly varying phase members add varying magnitudes of cylinderpowers between, e.g., 0.125 Diopters and 1.0 Diopter between the peakcorrective meridian Θ=0° (e.g., the astigmatic meridian) and thenon-peak corrective meridian Θ=45° in which minimum cylinder power isadded at Θ=0° (where the meridian is a mono-focal, shown at points1102), and in which the maximum cylinder power is added at Θ=45° wherethe meridian is configured as a bi-focal (shown along line 1104). Theadded power to the non-peak corrective meridian increases the toleranceof the IOL to misalignment from the corrective axis.

FIG. 12 illustrates a trifocal intraocular lens with the angularlyvarying phase members in accordance with an illustrative embodiment. Asshown in FIG. 12, the added varying cylinder power is added between thepeak corrective meridian Θ=0° and the non-peak corrective meridianΘ=45°, as shown in FIG. 11. As further shown, a trifocal optics 1202 isadded. The trifocal 1202 does not have an angularly varying phasemember.

FIG. 13 illustrates an ophthalmic apparatus 1300 having angularlyvarying phase members to extend tolerance of ocular astigmatism byvarying extended depth of focus at each meridian through an optimizedcombination of angularly and zonally diffractive phase structure on eachmeridian in accordance with an illustrative embodiment.

As shown in FIG. 13, the ophthalmic apparatus 1300 includes a firstcorrective meridian 90° *N°±α° (variable 01), where a is the extendedtolerance of the first corrective meridian, and N is an integer. ForN=0, 1, 2, 3, 4, the meridians includes 0° (1302), ±90° (1304), and 180°(1306). In some embodiments, α is ±3°, ±3.25°, ±3.5°, ±3.75°, ±4°, ±4°,±4.25°, ±4.5°, ±4.75°, ±5°, ±5.25°, ±5.5°, ±5.75°, ±6°, ±6.25°, ±6.5°,±6.75°, ±7°, ±7.25°, ±7.5°, ±7.75°, ±8°, ±8.25°, ±8.5°, ±8.75°, ±9°,±9.25°, ±9.5°, ±9.75°, and ±10°. Where a is ±10°, the IOL would have adynamic and optimized efficiency for correcting astigmatic effects thatcan tolerate misalignment of the cylindrical axis up to 10 (variable 08)degrees in either counter clockwise or clockwise rotation. It iscontemplated that terms noted as variables may be varied, modified, oradjusted, in some embodiments, to produce desired or intended effectsand benefits, as discussed herein.

FIG. 14 illustrates a table for a trifocal IOL configured with theangularly varying phase members. As shown in FIG. 14, the lighttransmission efficiency at a first corrective foci 1402 (e.g., at theretina) is about 100% while other foci along the same meridian is about0%. This configuration establishes the first corrective meridian 1402 at0=0° and other meridians, e.g., θ=±90° and, e.g., 180°, as a monofocalwith additional chromatic aberration reduction.

In addition, at meridian 45° *N°±α° (1408 and 1410) (variable 02), thelight transmission efficiency varies for three point of focus (shown as1408 a, 1408 b, and 1408 c) (e.g., at the front of the retina, at theretina, and behind the retina) of the optics at this meridian. For N=1,2, 3, 4, the meridians includes ±45° and ±90°. As shown in FIG. 14, atthe first foci (1408 a) (e.g., at the front of the retina), the lighttransmission efficiency is about 25% (variable 03), and the opticsincludes added power that matches the ocular astigmatic powercorresponding to the human astigmatism tolerance level. At the secondfoci (1408 b) (e.g., at the retina), the light transmission efficiencyis about 50% (variable 04) efficiency. At the third foci (1408 c) (e.g.,behind the retina), the light transmission efficiency is about 25%(variable 05), and the optics include added power having the samemagnitude as the first foci though with an opposite sign. At othermeridians, the focus on the retina has efficiency between 0.5% and 100%(variable 06) and the other focus not on the retina has efficiencybetween 0% and 25% (variable 07). In some embodiments, the lighttransmission efficiency are varied via different materials that may bestacked, e.g., as a stacking lens, where each layer is comprised of adifferent material. In other embodiments, the angularly-varying phasemembers may be comprised of a material or materials that have avariation in refractive index, a gradient index, or a programmed index,for example liquid crystal which creates transmission efficiency change.

The thickness profile T₁(r, θ) for the IOL may be characterized byEquation 2 below.T ₁(r,θ)=t ₁(r)|COS²(θ)|+t ₂(r)|SIN²(θ)|  (Equation 2)

According to Equation 2, t₁(r) and t₂(r) are step heights for each zone,and they each matches an optical path difference (OPD) from −2λ to 2λ,where λ is the design wavelength at zonal radius r.

Equation 2 may be simplified and represented as Equation 3, where A isadjusts the size of the extended operating band of the angularly varyingphase member, and B provides an offset of the center of the angularlyvarying phase member with respect to a pre-defined reference frame(e.g., Θ=0° or Θ=90°, etc.).T ₁(r,θ)=COS[Aθ+B]  (Equation 3)

Example: Angularly Varying Phase Members that Varies Along AngularPosition

FIGS. 15-18, comprising, FIGS. 15A, 15B, 16A, 16B, 16C, 17A, 17B, 18A,18B, and 18C, depict the ophthalmic apparatus with angularly varyingphase members in accordance with other illustrative embodiments.According to these embodiments, the angularly varying phase members arelocated with a fixed-size zone and varies only along the angularposition. In FIGS. 15A, 15B, 16B, 16C, 17A, 17B, 18B, and 18C, heightprofiles are illustrated via representative echelette elements for adiffractive surface.

As shown in FIGS. 15A-15B, the ophthalmic apparatus includes a pluralityof zones 1502 (shown as 1502 a, 1504 b, and 1504 c). The zones 1502 a,1502 b, 1502 c defined at a first corrective meridian θ=0° and 180°(1506) has approximately the same zone length (i.e., cylinder power) asthe zones 1502 a, 1502 b, 1502 c defined at a second meridian θ=45° and135° (1508). As further shown in FIGS. 16A, 16B, and 16C, the heightprofile (shown as 1602, 1604, 1606, 1608, 1610, and 1612) of the face ofthe lens varies along the angular position θ=0°, θ=9°, θ=18°, θ=27°,θ=36°, and θ=45°.

FIGS. 17A and 17B illustrate an ophthalmic apparatus having a heightprofile across the multiple zones (shown as 1702 a, 1702 b, and 1702 c)in which the height of the face of the lens angularly varies with themeridian axes. As shown in FIGS. 18A, 18B, and 18C, the height profile(shown as 1802, 1804, 1806, 1808, 1810, and 1812) of the face of thelens varies along the angular position θ=0°, θ=9°, θ=18°, θ=27°, θ=36°,and θ=45°.

Referring back to FIG. 13, in another aspect, the ophthalmic apparatusincludes a plurality of alignment markings, including a first set ofalignment markings 1302 and a second set of alignment markings 1304,that indicate the corrective meridian of the lens. In some embodiments,the first set of alignment markings 1302 is located at the meridian θ=0°and 180°. The second set of alignment markings 1304 may includecorresponding sets of markets to define a tolerance band for the lens.In some embodiments, the second set of alignment markings 1304 islocated at ±5° radial offset from the first set of alignment markings1302.

Example: Refractive Lens Surfaces with Angularly Varying Phase Members

FIGS. 19A and 19B are diagrams of an exemplary ophthalmic apparatus 1900that includes refractive angularly-varying phase members 102 inaccordance with another illustrative embodiment. A height profile 1902(shown as 1902 a and 1902 b) of the refractive surface 1904 (shown as1904 a and 1904 b) is shown at 0=0° and 0=45°. As shown in FIG. 19A, thefirst height profile 1902 a of the lens transitions into the secondheight profile 1904 b. Here, the inflection point of the refractivesurface is shown to vary spatially (i.e., changing radial values) andangularly (i.e., changing height or thickness values).

FIGS. 20A, 20B, 20C, 20D, and 20E illustrate a plurality of exemplaryheight profiles of the anterior or posterior face across the angularlyphase members of the ophthalmic apparatus of FIGS. 19A-19B, inaccordance with an illustrative embodiment. That is, the height profileis shown between the first high power meridian (at Θ=0°) and theoperational edge of the angularly varying phase members (e.g., at Θ=±α,e.g., Θ=10° and Θ=−10°) in accordance with an illustrative embodiment.In FIG. 20B, representative height profiles at Θ=0° (2002); Θ=2° (2004);Θ=4° (2006); Θ=6° (2008); Θ=8° (2010); and Θ=10° (2012) (also shown inFIG. 20A) are provided as cross-sections of the echelette at thedifferent meridians shown in FIG. 20A. As shown, the height profiles ataxes nearby to the first high power meridian (e.g., between ±10°) have asimilar shape, as the first high power meridian. The height profilevaries in a continuous gradual manner (e.g., having a sine and cosinerelationship) along the radial direction. This can be observed in FIGS.20B and 20C. In FIG. 20B, the overall refractive profile is shown, andin FIG. 20C, an inflection point 2014 (e.g., shown as points 2014 a,2014 b, 2014 c, 2014 d, 2014 e, and 2014 f) defined at a given zoneboundary is shown. This transition of the inflection points 2014 may bedescribed as a cosine-based or sine-based function, or a functionderived from a combination thereof.

The thickness profile T1(r, θ) for the refractive design may becharacterized by Equation 4 below.T ₁(r,θ)=t ₁(r)|COS²(θ)|+t ₂(r)|SIN²(θ)|  (Equation 4)

According to Equation 4, t₁(r) and t₂(r) are the add power for eachzone, and they each match optical power needs from −200D to +5.0D, for adesign wavelength at zonal radius r.

FIG. 20C illustrates a first portion of the height profiles (near theoptical axis) at Θ=0° (202); Θ=2° (204); Θ=4° (206); Θ=6° (208); Θ=8°(210); and Θ=10° (212) superimposed next to one another. This variationof the height profile along the radial axis provides a lens region thatfocuses light at the desired foci and other foci nearby. To this end,radial offset (i.e., misalignment) of the ophthalmic apparatus from thecenter axis of a desired corrective meridian results in its nearbyregions focusing the light to the desired foci.

In FIGS. 20D and 20E, example height profiles of the lens surfacebetween Θ=0° and Θ=45° are shown. As shown in FIGS. 20D and 20E, theheight profiles of the angularly varying phase member vary as acosine-based or sine-based function. In some embodiments, the heightprofiles of the lens surface between Θ=45° and Θ=90° are mirrored atΘ=45° to the lens surface between Θ=0° and Θ=45°.

It is contemplated that refractive angularly varying phase member canvary symmetrically or asymmetrically, for a given zone, as well asbetween the multiple zones, as described, for example, in relation toFIGS. 8, 9, 16, and 18. That is, inflection points in the refractivesurface at a given zone (e.g., a first zone) may vary, in the radial andangular direction, at the same rate with inflection points in therefractive surface at another zone (e.g., a second zone), as describedin relation to the diffractive element of FIG. 8. In addition, in someembodiments, inflection points in the refractive surface at a given zone(e.g., a first zone) may vary, in the radial and angular direction, at adifferent rate with inflection points in the refractive surface atanother zone (e.g., a second zone), as described in relation to thediffractive element of FIG. 9. In addition, in some embodiments,inflection points in the refractive surface at a given zone (e.g., afirst zone) may vary, only in the angular direction, at a same ordifferent rate with inflection points in the refractive surface atanother zone (e.g., a second zone), as described in relation to thediffractive element of FIGS. 16 and 18.

Example: Multi-Focal Refractive Ophthalmic Apparatus with Diffractive orRefractive Angularly Varying Phase Members

FIG. 21, comprising FIGS. 21A, 21B, and 21C, is a diagram illustratingan exemplary ophthalmic apparatus 2100 that includes refractive ordiffractive angularly-varying phase members 102, in accordance withanother illustrative embodiment.

The angularly-varying phase member 102, in FIG. 21, can be characterizedas Equation 5, where r(θ) is the contour radius for the given meridianadded power A(θ), wavelength λ, zone number n, and the scaling values(θ), all at meridian θ.

$\begin{matrix}{{r(\theta)} = \sqrt{2 \cdot n \cdot \frac{{s(\theta)} \cdot \lambda}{A(\theta)}}} & \left( {{Equation}\mspace{14mu} 5} \right)\end{matrix}$

In FIG. 21A, the lens 2100 provides a mono-focal at corrective meridianΘ=0° and 180°. In addition, the lens 2100 provides a second mono-focalat corrective meridian Θ=90° and −90°. In some embodiments, themono-focal corrective meridian Θ=0° and 180° and the mono-focalcorrective meridian Θ=90° and −90° have the same focal point. In otherembodiments, the mono-focal corrective meridian Θ=0° and 180° and themono-focal corrective meridian Θ=90° and −90° have different focalpoints.

Referring still to FIG. 21A, the lens 2100 provides a first bi-focal atΘ=−45° and 135° and, in addition, the lens 2100 provides a secondbi-focal at Θ=45° and −135°. In some embodiments, the bi-focalcorrective meridian −45° and 135° and the bi-focal corrective meridianΘ=45° and −135° have the same focal point. In other embodiments, thebi-focal corrective meridian −45° and 135° and the bi-focal correctivemeridian 45° and −135° have different focal points.

As shown in FIG. 21B, intraocular lens 2100 has a base cylindrical power(e.g., 6.0 Diopters) to which angularly varying phase members havingadditional cylindrical power are added. The angularly varying phasemembers adds the cylindrical power having an extended tolerance ofoperation, for example, up to ±10° (of misalignment) from a givencorrective meridian (e.g., an astigmatism meridian). As shown, theadditional cylindrical power are added to a surface sag coordinate(shown as “sag(z)”). Specifically, the added cylindrical power (shown as“Value θ” in FIG. 21B), for each given angular position θ (2104), inthis exemplary lens design, varies between about −200 Diopters and about−0.01 Diopters (shown as “Value θ” 2104) and between about 0.01 Dioptersand about 6.0 Diopters (shown as “Value θ” 2106). The added power isprovided over the surface of the intraocular lens having a diameter 2108of 6.0 mm (millimeters). Radial positions 2114 (shown as 2114 a and 2114b) are illustratively shown in FIGS. 21A and 21B. As shown in FIG. 21C,the added cylindrical power, along each radial positions (e.g., atΘ=−180° to Θ=180°), at radial positions 2114 a and 2114 b are provided.

Referring still to FIG. 21B, the added cylindrical power of 0.01Diopters and about 6.0 Diopters and of −200 Diopters and about −0.01Diopters is added via a refractive surface 2110 (e.g., as shown havingan “ETA(r, θ) surface profile”). As shown in FIG. 21B, the refractivesurface 2110 has a modified thickness value at sag surface value of “0”at the center of the lens. The sag surface value, as shown, decreases togenerate the refractive surface profile, as for example, described inrelation to FIG. 4D. It should be appreciated that the provided sagsurface profile is merely illustrative. It is contemplated thatequivalent refractive surfaces may be produced on various lens surfacein additive or subtractive manner, as shown, for example, but notlimited to, in relation to FIGS. 4A-4D.

Referring still to FIG. 21B, the added cylindrical power profile 2112may be used to provide distant vision and emmetropia correction for agiven patient. Emmetropia generally refers to a state in which the eyeis relaxed and focused on an object more than 20 feet away in whichlight coming from the focus object enters the eye in a substantiallyparallel, and the rays are focused on the retina without effort. To thisend, image at all meridian can reach 20/20 “uncorrected distance visualacuity” (UDVA).

Referring to back to FIG. 21A, the added cylindrical power profile 2112of FIG. 21B is added at angular position Θ=Θ° (shown as “Θ=Θ° 2116”). Tothis end, the angularly varying phase members, as described herein, forexample, including those described in relation to FIGS. 1-2, 7-9, and15-20 may be applied at any angular position along the lens surface, togenerate a multi-focal lens.

Referring still to FIG. 21A, in some embodiment, a complementaryangularly varying phase member may be added in a given quadrant of thelens. For example, an intraocular lens may include a first angularlyvarying phase member at an angular position between Θ=45° and Θ=90°; theintraocular lens may include a second angularly varying phase member atan angular position between Θ=0° and Θ=45° in which the second angularlyvarying phase member is mirrored, along the axis Θ=45°, with respect tothe first angularly varying phase member.

Example: Alignment Markings for Extended Tolerance Band

FIGS. 22A and 22B depicts an ophthalmic apparatus with an extendedtolerance astigmatic band. The ophthalmic apparatus includes the secondset of alignment markings 1308 as discussed in relation to FIG. 13.

Example Method of Generating Surfaces with Angularly-Varying PhaseMembers

FIG. 23 is diagram of a method 2300 to generate, via a processor, thesurface with the angularly-varying phase members, in accordance with anillustrative embodiment. As shown in FIG. 23, the method 2300 includesgenerating (2302), via a processor, an initial design (2304) comprisinga base surface (with base cylindrical power) and sectional enhancements(with added cylindrical power) and iteratively generating (2308) andevaluating, a revised design (2310), generated according to anoptimization routine (2308) that is performed based on sectionalparameters, until pre-defined image quality metric values and boundaryparameter are achieved. The sectional enhancements power of the initialdesign and the iterative design is the surface with theangularly-varying phase members.

Referring still to FIG. 23, the method 2300 includes generating (2302) afirst design (2304) via i) initial surface optical parameter, includinga) base surface optical parameters 2312 and b) sectional surface opticalparameters 2314, and ii) the pre-defined image quality metric values2316. The base surface optical parameters 2312 include, in someembodiments, parameters associated with a radius of curvature for thetoric lens (shown as “Radius of curvature” 2318), parameters associatedwith conic constant and aspheric coefficients (shown as “Conic constant”2320), parameters associated with base cylinder power (shown as“Cylinder power” 2322), and parameters associated lens and/or coatingmaterial characteristics such as refractive index (shown as “Refractiveindex” 2324). Other parameters may be used as part of the base surfaceoptical parameters 2312. The section surface optical parameters 2314, insome embodiments, includes parameters associated with sectional addedpower and meridian characteristics (shown as “Sectional add power” 2328)and parameters associated with high order aberration characteristics,e.g., Zernike aberrations above second-order (shown as “High orderaberrations” 2328).

Referring still to FIG. 23, the parameters associated with the sectionaladded power 2326, in some embodiments, include a cylindrical power, fora given optical zone. In some embodiments, the cylindrical power for theadded power are all refractive, all diffractive, or a combination ofboth. The parameters associated with the high order aberrationcharacteristics 2328, in some embodiments, include polynomial values(e.g., based on Zernike polynomials, Chebyshev polynomials, andcombinations thereof) or characteristics such as polynomial orders andtypes as well as meridian boundaries for the high order aberrations. Thehigh order aberration is constraint, e.g., from minimum to maximumcylindrical power over one or more meridian sections. In someembodiments, the high order aberrations is constraint or designated to ameridian, e.g., that corresponds to a corneal irregular geometry orlimited retinal area functions. Such customization has a potential totruly benefit patients having cornea with or without astigmatism,patients with local Keratoconus with or without astigmatism, patientswith glaucoma, patients with retinal macular degeneration (AMD), and thelike.

Referring still to FIG. 23, the parameters associated with thepre-defined image quality metric value 2316 includes parametersassociated with expected image quality metric (shown as “Expected imagequality metric values” 2330) and parameters associated with specialboundary restrain parameters (shown as “Special boundary restrainparameters” 2332). In some embodiments, image quality metric is based acomparison of a base polychromatic diffraction MTF (modular transferfunction) (e.g., tangential and sagittal) to a number of errorpolychromatic diffraction MTFs values, e.g., where one or morepolychromatic diffraction MTFs are determined for one or moremisalignments of the generated toric lens from its intended operatingmeridians, e.g., at 5-degree misalignment and at 10-degree misalignment.

Referring still to FIG. 23, the initial design (2304) is evaluated (2334a) to determine image quality metric values (e.g., the basepolychromatic diffraction MTF, e.g., at 0 degree misalignment) and theerror polychromatic diffraction MTFs, e.g., at the 5 and 10 degreesmisalignment) and boundary parameters. The determined image qualitymetric values are evaluated (2336) to determine whether the imagequality metric values and boundary parameters meet an expected outcome,e.g., a value of 0.2. In some embodiments, the expected outcome iswhether there is no cut off through spatial frequency beyond 100 cpd.Upon determining that the condition is met, the method 2300 is stop(2338). It is contemplated that other image quality metrics may be used,e.g., the optical transfer function (OTF), phase transfer function(PhTF), and etc.

Where the condition is not met, the method 2300 adjusts (2308) sectionalparameters to be optimized and rerun the optimization to generate therevised design 2310. In some embodiments, the adjusted sectionalparameters may include power A(θ), wavelength λ, zone number n, and thescaling value s(θ), as for example, shown in FIGS. 19A-19B, 20A-20E,21A-21C, which is expressed as

${{r(\theta)} = \sqrt{2 \cdot n \cdot \frac{{s(\theta)} \cdot \lambda}{A(\theta)}}},$where r(θ) is the contour radius for the given meridian added powerA(θ), wavelength k, zone number n, and the scaling value s(θ), all atmeridian θ.

Referring back to FIG. 23, the method 2300 then includes evaluating(2334 b) the revised design 2310 to determine image quality metricvalues (e.g., the base polychromatic diffraction MTF, e.g., at 0 degreemisalignment) and the error polychromatic diffraction MTFs, e.g., at the5 and 10 degrees misalignment) and boundary parameters, as discussed inrelation to step 2334 a, and re-evaluating (2336) whether the revisedimage quality metric values and boundary parameters meet the expectedoutcome, as discussed in relation to step 2336.

In some embodiments, the method 2300 is performed in an optical andillumination design tool such as Zemax (Kirkland, Wash.). It iscontemplated that the method 2300 can be performed in other simulationand/or design environment.

Ophthalmic Apparatus Having Extended Tolerance Band with FreeformRefractive Surfaces

FIG. 24 is a diagram of an example freeform-polynomial surface area 2402that provides extended rotational tolerance, in accordance with anillustrative embodiment. The freeform-polynomial surface area 2402 ismapped to a surface of an ophthalmic apparatus 324 (not shown—see FIG.4) to provide cylinder power to the ophthalmic apparatus, e.g., for thecorrection an astigmatism, or the like, such that the ophthalmicapparatus can be subjected to a cylindrical axis misalignment (CAM)(shown via arrow 2406) of the meridian 2404 (also referred to as “axis’2404) of up to 10 degrees without degradation of the correctiveperformance (e.g., with regard to visual acuity (VA) or modular transferfunction (MTF)), as compared to when there no misalignment.

Notably, the freeform-polynomial surface area 2402 is defined as amathematical expression that is a combination of one or more polynomialexpressions each having a distinct complex orders. Examples ofpolynomial expressions includes, but are not limited to, Chebyshev-basedpolynomial expression, Zernike-based polynomial expression. Thecombination of one or more polynomial expressions may be used to definean angularly-varying phase member that is tolerant of cylindrical axismisalignment (CAM) up to an extended band of operation withoutdegradation of the corrective performance such as visual acuity (VA) ormodular transfer function (MTF) as compared to when there nomisalignment.

In some embodiments, one or more polynomial expressions are combinedwith different complex orders and the results are tested to determinethat corrective performance (e.g., with regard to visual acuity (VA) ormodular transfer function (MTF) are met.

As used herein, a “Chebyshev-based polynomial” refers to a mathematicalexpression that is expressed as a combination of one or more Chebyshevpolynomial components in which the Chebyshev polynomial components is aChebyshev polynomials of the first kind and/or a Chebyshev polynomialsof the second kind. The Chebyshev polynomial can include, as acombination, the Chebyshev polynomial component along with anotherpolynomial expression (e.g., Zernike polynomials, combinations ofZernike polynomials, other polynomials, or combination thereof, andetc.)

As used herein, a “Zernike-based polynomial” refers to a mathematicalexpression that is expressed as a combination of one or more Zernikepolynomial components in which the Zernike polynomial components is aZernike polynomial. The Zernike polynomial can include, as acombination, a Zernike polynomial component along with anotherpolynomial expression (e.g., Chebyshev polynomials, combinations ofChebyshev polynomials, other polynomials, or combination thereof, andetc.)

Referring back to FIG. 24, the freeform-polynomial surface area 2402 ofFIG. 24 is defined as a mathematical expression that is a combination ofone or more polynomial expressions each having a distinct complexorders. In some embodiments, the freeform-polynomial surface area 2402is defined as a second thickness value T(x,y) for a cylinder surfacesuperimposed on a first thickness value (e.g., a base or typicalaspheric height profile), in which T(x, y) is defined by Equation 6:T(x,y)={c(i,j)*cos(i*arccos(t))*cos(j*arccos(t))}  (Equation 6)where c(i, j) is a coefficient based on i and j, which are each ordersof the polynomial and expressed as integers, x and y are spatiallocations on the freeform-polynomial surface area, and t is a normalizedparameter for angular positions having values between −1.0 and 1.0. Thebase thickness value can be from a typical aspheric thickness profile.In some embodiments, the coefficient c(i,j) is based on a basis functionthat adjust the normalized amplitudes of each respective location of thelens as represented by the Chebyshev polynomial. A Chebyshev polynomial(of the first kind), along one dimension, can be expressed asT_(k)(x)=cos(k*cos⁻¹(x)), where k is an order that is an integer. In twodimension, a Chebyshev polynomial (of the first kind) can be expressedas T_(ij)(x, y)=COS(i*cos⁻¹(x))*COS(j*cos⁻¹(y)), where x and y valueshave a numerical value between −1.0 and +1.0, and Tij are normalized toa value of −1.0 and +1.0.

Referring still to FIG. 24, the freeform-polynomial surface area 2402 ofFIG. 24 is derived from Chebyshev polynomials as shown in Equation 6having i-order of 0 to 6 and a j-order of 0 to 6. Equation 7 shows theexpanded mathematical expression for the second freeform-polynomialsurface area 2402 of FIG. 24.

$\begin{matrix}{{T\left( {x,y} \right)} = {{{{c\left( {0,0} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,1} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,2} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {2^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,3} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {3^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,4} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,5} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,6} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,0} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,1} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,2} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {2^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,3} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {3^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,4} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,5} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,6} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}} + \mspace{14mu}{\ldots\mspace{14mu}{c\left( {6,0} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,1} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,2} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {2^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,3} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {3^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,4} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,5} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,6} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}}} = {{c\left( {0,0} \right)} + {{c\left( {0,1} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}} + {{c\left( {0,2} \right)}^{*}{\cos\left( {{\cos\;\left( {2^{*}{\cos^{- 1}(t)}} \right)} + {{c\left( {0,3} \right)}^{*}\cos\;\left( {3^{*}{\cos^{- 1}(t)}} \right)} + {c\left( {0,4} \right)^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {0,5} \right)}^{*}\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)} + {{c\left( {0,6} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,0} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}} + {{c\left( {1,1} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}} + {{c\left( {1,2} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {2^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,3} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {3^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,4} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,5} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {1,6} \right)}^{*}{\cos\left( {\cos^{- 1}(t)} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}} + \mspace{14mu}{\ldots\mspace{14mu}{c\left( {6,0} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {0^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,1} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {1^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,2} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {2^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,3} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {3^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,4} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {4^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,5} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {5^{*}{\cos^{- 1}(t)}} \right)}} + {{c\left( {6,6} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}^{*}{\cos\left( {6^{*}{\cos^{- 1}(t)}} \right)}}} \right.}}}}} & \left( {{Equation}\mspace{14mu} 7} \right)\end{matrix}$

Referring still to FIG. 24, a power pupil map with uniformly distributedcontour lines of the calculated cylindrical power for thefreeform-polynomial surface area 2402 is shown. The corrective meridianis located at about Θ=0° (shown as axis 104) with a center portion ofthe freeform-polynomial surface area 2402 being disposed at this Θposition. Off-center structures of the freeform-polynomial surface area2402 extend from the center structure in a gradually varying manner(e.g., as defined by the combination of Chebyshev polynomials describedin relation to Equation 7) to apply cylinder power to a band ofmeridians surrounding the corrective meridian enabling the ophthalmicapparatus to operate off-axis (or off-meridian) to the correctivemeridian (e.g., the astigmatism meridian). Notably, there are no morethan 0.6-Diopter difference between any neighboring uniformlydistributed contour lines.

FIG. 25 illustrates an example operation of the freeform-polynomialsurface area of FIG. 24 when subjected to misalignment, in accordancewith an illustrative embodiment. The freeform-polynomial surface area2402, as a diffractive or refractive structure, in some embodiments,varies the extended depth of focus to a plurality of nearby focuspoints. To this end, light directed to such nearby focus points are thusdirected to the desired focus point when the ophthalmic apparatus issubjected to a rotational offset from a primary intended axis ofalignment, thereby extending the rotational tolerance of the apparatusto an extended tolerance band. In FIG. 25, a portion (2502) of thefreeform-polynomial surface area 2402 has a focus point 2504 (e.g.,referred to as a “main focus point” 2504, e.g., to correct for anastigmatism) that is generated by a region about the center 2506 of theportion 2502 of the freeform-polynomial surface area 2402. In thisexample, a nearby region 2508 of that portion 2502 has a focus point2510 (e.g., referred to as an “auxiliary focus point” 2510) that isoffset from the main focus point 2504. When the freeform-polynomialsurface area 2402 is rotated about axis 2512, e.g., as misalignment 2402is introduced to the corrective meridian Θ=0° (2404), the focus point2510 of region 2508 is moved towards the main focus point 2504, therebyextending the band of operation of the freeform-polynomial surface area2402. Remarkably, this extended tolerance astigmatism band deliverscylinder power to correct for the astigmatism for a range of meridians(e.g., up to ±10° as shown in FIG. 24, though can be more in otherembodiments), thereby eliminating any need for additional correctivemeasures (e.g., supplemental corrective devices or another surgicalintervention) when the implanted ophthalmic apparatus is not perfectlyaligned to the desired astigmatism meridian in the eye.

Put another way, the freeform-polynomial surface area 2402 facilitatesan extended band of the corrective meridian that has minimal, and/orclinically acceptable, degradation of the visual acuity and modulationtransfer function when the ophthalmic apparatus is subjected torotational misalignment between the astigmatic axis and a center axis ofthe corrective meridian.

Corneal Irregular Geometry or Limited Retinal Area Functions

In another aspect, the freeform-polynomial surface area 2402 of FIG. 24is optimized to purposely place accumulated high surface amplitude tonon-functional retinal area so that the functional areas can fullybenefit the enhanced image quality stability of the freeform-polynomialsurface design. Examples of non-functional retinal areas may include,but not limited to, areas of gradual loss of sight (e.g., associatedwith glaucoma or retinal macular degeneration (e.g., age-related maculardegeneration, AMD). The freeform-polynomial surface area 2402 of FIG. 24can be similarly optimized to emphasize needs for a cornea thatirregularly shaped with or without astigmatism and with localKeratoconus with or without astigmatism.

In particular, the freeform-polynomial surface area 2402, in someembodiments, are optimized by further modification of the weights (e.g.,c(i,j) as discussed in relation to Equation 6 or Equation 7) in thecombined Chebyshev polynomials and the Zernike or extended polynomialsused to characterize or design the geometry of the freeform-polynomialsurface area 2402. As noted above, the c(i,j) is used to scale thenormalized surface generated by the Chebyshev polynomials or the Zernikepolynomials. C(i,j) is also used to adjust and/or emphasize cylindricalpower for corneal irregular geometry or limited retinal area functions.

As shown in Equations 6 and 7, the freeform-polynomial surface area 2402is defined by a surface sag (or power) that is a weighted sum ofChebyshev polynomials (Zernike and other polynomials may be used with,or in substitute of, the Chebyshev polynomials) with the coefficientc(i, j) (e.g., shown in Equation 6).

The coefficient c(i, j) are weights that may be modified or set based onspecific knowledge of the local coordinates of the special corneairregularity. To this end, the coefficient c(i, j) allows the specificpolynomials to be freely shifted in space (i.e., spatial) domain tomatch the local coordinates. The coefficient c(i, j) as weights for eachpolynomial can be a function of local coordinates function andimplemented as a filter with low-, medium-, or high-pass transmissionoperations.

Results of IOL with Exemplified Freeform-Polynomial Surfaces

FIG. 26 shows a combined cylinder map generated from the combination ofthe IOL cylindrical power (provided, in part, via thefreeform-polynomial surface) combined with the corneal cylindrical powerthrough meridians. As discussed above with reference to FIG. 24, and ascan be seen from the IOL cylinder map through meridians around theclock, there is remarkably no more than about 0.6D difference for anycontinuous uniformly distributed contour lines at the IOL plane. The IOLSE is 20D at the IOL plane. The IOL cylinder map of FIG. 24 is combinedwith the IOL SE to provide the overall IOL cylindrical map. This overallIOL cylindrical map is then combined with a test corneal cylindricalpower. The resulting combination (shown in FIG. 26) remarkably showslittle variation in the cylinder map of the combined IOL cylindricalpower the corneal cylindrical power. That is, the astigmatism associatedwith test corneal cylindrical power has been attenuated and/or correctedfor by the IOL cylindrical power provided, in part, by thefreeform-polynomial surface.

FIGS. 27A and 27B each shows calculated MTF values as spatialfrequencies of an exemplified IOL in a physiological eye model withastigmatic cornea in different cylindrical axis misalignment (CAM)situations between the cornea and the IOL for an iris pupil. Notably, asshown in FIGS. 27A and 27B, the modulation transfer function (MTF) ismaintained across the extended range of alignment for a lens configuredwith the freeform-polynomial surface area 2402 of FIG. 24. Specifically,in FIGS. 27A and 27B, the MTFs for misalignment at 0 degrees, 5 degrees,and 10 degrees are shown (shown as “CAM=0 Deg” 2702, “CAM=5 Deg” 2704,and “CAM=10 Deg” 2706). In FIG. 27A, the iris pupil is about 3.0 mm. InFIG. 27B, the iris pupil is about 5.0 mm.

Notably, as can also be seen from the MTF curves, there are no cut-offsof the spatial frequency beyond 100 cpd (cycles per degree), which foran IOL with SE (Spherical Equivalent) of 20D (Diopters), this spatialfrequency is approximately 30 cpd.

Example of Multi-Zonal IOL with the Exemplified Freeform-PolynomialSurfaces

In another aspect, a multi-zonal IOL with freeform-polynomial surfacesis disclosed. In some embodiments, the multiple zonal structure includesone or more zonal surfaces defines by Chebyshev-based polynomials whileother zonal surfaces are defined by other polynomials (e.g., Zernike andChebyshev polynomials).

In some embodiments, the freeform-polynomial surface area (e.g., thesecond or third height profile) symmetrically spans part of the opticalface of the apparatus). FIG. 28A shows a diagram of afreeform-polynomial surface area (e.g., the second or third heightprofile) of a second optical zone that symmetrically spans part of theoptical face of the apparatus, in accordance with an illustrativeembodiment.

As shown in FIG. 28A, the ophthalmic apparatus includes an optical face2802 (e.g., the portion of the face surface of the ophthalmic apparatusthat include corrective optical structures) that includes the one ormore optical zones 2804 (shown as “optical zone 1” 2804 a and “opticalzone 2” 2804 b). The first zone of the optical face has a boundarydefined by a first axis 2806 of the face and a second axis 2808 of theface (e.g., wherein the first axis is orthogonal to the second axis),and each of the x-spatial locations at value −1.0 and at value 1.0 islocated at a first radial position along the first axis between a centerlocation 2810 of the ophthalmic apparatus and the boundary, and each ofthe y-spatial locations at value −1.0 and at value 1.0 is located at thefirst radial position along the second axis between the center locationof the ophthalmic apparatus and the boundary. As shown, the “opticalzone 1” 2804 a has a first T(x,y) height profile (e.g., as described inrelation to Equation 6) that is superimposed over, e.g., the base ortypical aspherical height profile. In some embodiments, the “opticalzone 1” 2804 a has a surfaces defined by other polynomials (e.g.,Zernike, or combination of Zernike and Chebyshev polynomials).

In some embodiments, the second “optical zone 2” 2804 b is characterizedby a third height profile T₂(x,y) (e.g., an extra height profileassociated with cylinder power) superimposed on a first height profile(e.g. a base or typical aspheric height profile), the third heightprofile being defined as:T ₂(x,y)=Σ{c ₂(i ₂ ,j ₂)*cos(i ₂*arccos(t ₂))*cos(j ₂*arccos(t ₂))}  (Equation 8)where c₂(i₂, j₂) is a coefficient based on i₂ and j₂, which are eachintegers (e.g., ranging between 0 and 10), x and y are spatial locationson the second freeform-polynomial surface area and has values between−1.0 and 1.0, and t₂ is a normalized parameter having values between−1.0 and 1.0 (e.g., associated with the intended correction meridian).In some embodiments, the “optical zone 2” 2804 b has a surfaces definedby other polynomials (e.g., Zernike, or combination of Zernike andChebyshev polynomials).

In some embodiments, the freeform-polynomial surface area (e.g., thesecond or third height profile) asymmetrically spans part of the opticalface of the apparatus. That is, the first zone of the optical face has aboundary defined by a first axis of the face and a second axis of theface (e.g., wherein the first axis is orthogonal to the second axis).Each of the x-spatial locations at value −1.0 and at value 1.0 islocated at a first radial position along the first axis between a centerlocation of the ophthalmic apparatus and the boundary, and each of they-spatial locations at value −1.0 and at value 1.0 is located at asecond radial position along the second axis between the center locationof the ophthalmic apparatus and the boundary, where the first radialposition and the second radial position are different.

FIG. 28B shows a diagram of a freeform-polynomial surface area (e.g.,the second or third height profile) of a second optical zone thatsymmetrically spans part of the optical face of the apparatus, inaccordance with an illustrative embodiment.

As shown in FIG. 28B, the ophthalmic apparatus includes the optical face2802 (e.g., the portion of the face surface of the ophthalmic apparatusthat include corrective optical structures) that includes the one ormore optical zones 28004 (shown as “optical zone 1” 2804 a and “opticalzone 2” 2804 b) that are asymmetric one another. The first zone of theoptical face has a boundary defined by a first axis 2806 of the face anda second axis 2808 of the face (e.g., wherein the first axis isorthogonal to the second axis), and each of the x-spatial locations atvalue −1.0 and at value 1.0 is located at a first radial position alongthe first axis between a center location 2810 of the ophthalmicapparatus and the boundary, and each of the y-spatial locations at value−1.0 and at value 1.0 is located at the first radial position along thesecond axis between the center location of the ophthalmic apparatus andthe boundary. As shown, the “optical zone 1” 2804 a has a first T(x,y)height profile (e.g., as described in relation to Equation 1) that issuperimposed over, e.g., the base or typical aspherical height profile.In some embodiments, the “optical zone 1” 2804 a has a surfaces definedby other polynomials (e.g., Zernike, or combination of Zernike andChebyshev polynomials).

In some embodiments, the second “optical zone 2” 2804 b is characterizedby a third height profile T₂(x,y) (e.g., as described in relation toEquation 7) that are each superimposed over, e.g., the base or typicalaspherical height profile. In some embodiments, the “optical zone 2”2804 b has a surfaces defined by other polynomials (e.g., Zernike, orcombination of Zernike and Chebyshev polynomials).

It is contemplated that other zone shapes may be used for a given zoneof the multiple zones. Example of other zone shape include, but notlimited to, a rectangle, diamond, and various freeform polygons.

Referring back to FIG. 23, the diagram also shows a method to generate,via a processor, the freeform-polynomial surface area of FIG. 24, inaccordance with an illustrative embodiment. As shown in FIG. 23, themethod includes generating (2302), via a processor, an initial design(2304) comprising a base surface (with base cylindrical power) andsectional enhancements for freeform-polynomial surface area—with addedcylindrical power derived from the Chebyshev-based polynomialexpression, Zernike-based polynomial expression—and iterativelygenerating (2306) and evaluating, a revised design (2310), generatedaccording to an optimization routine (2308) that is performed based onsectional parameters, until pre-defined image quality metric values andboundary parameter are achieved. The sectional enhancements power of thefreeform-polynomial surface area initial design and the iterativefreeform-polynomial surface area design are the ETA polynomial surfaceof FIG. 24.

Referring still to FIG. 23, the parameters associated with the sectionaladded power 2326 for the freeform-polynomial surface area, in someembodiments, include a mathematical expression comprising a combinationof one or more polynomial expressions (e.g., Chebyshev-based polynomialexpression, Zernike-based polynomial expression, etc.) each having adistinct complex orders. In some embodiments, the cylindrical power forthe added power are all refractive. The parameters associated with thehigh order aberration characteristics 1128, in some embodiments, includepolynomial values (e.g., based on Zernike polynomials, Chebyshevpolynomials, and combinations thereof) or characteristics such aspolynomial orders and types as well as meridian boundaries for the highorder aberrations. The high order aberration is constrained, e.g., fromminimum to maximum cylindrical power over one or more meridian sections.In some embodiments, the high order aberrations is constrained ordesignated to a meridian, e.g., that corresponds to a corneal irregulargeometry or limited retinal area functions. In other embodiments, thehigh order aberrations may be introduced as weights a freeformpolynomial weights to form the freeform-polynomial surface area. In suchembodiments, the high order aberrations and its meridian locations onthe lens surface may be optimized prior to the freeform polynomialweights being determined to facilitate a customized design that istailored for a given patient (i.e., particularly in view of cornealirregular geometry or limited retinal area functions). Suchcustomization has a potential to truly benefit patients having corneawith or without astigmatism, patients with local Keratoconus with orwithout astigmatism, patients with glaucoma, patients with retinalmacular degeneration (AMD), and the like.

The adjusted sectional parameters (e.g., 2308) may include adjustingvalues for i and j of the Chebyshev or Zernike polynomials, as discussedin reference to Equation 6 or Equation 7. In some embodiments, only onevalue of i or j of the Chebyshev or Zernike polynomials is adjusted togenerate each design variant. In other embodiments, the values of i andj of the Chebyshev or Zernike polynomials are adjusted concurrently.

Ophthalmic Apparatus with Extended Tolerance Band by ModifyingRefractive Powers in Uniform Meridian Distribution

FIG. 29 is a diagram of cylindrical map of a polynomial surface 2902(also referred to as an ETA polynomial surface 2902) that is uniformlyarranged over a plurality of meridians that provides extended rotationaltolerance, in accordance with an illustrative embodiment. The polynomialsurface 2902 is mapped to a surface of an ophthalmic apparatus 324 (notshown—see FIG. 4) to provide cylinder power to the ophthalmic apparatus,e.g., for the correction an astigmatism, or the like, such that theophthalmic apparatus can be subjected to a cylindrical axis misalignment(CAM) (shown via arrow 2904) of the meridian 2906 a of up to 10 degreeswithout degradation of the corrective performance (e.g., with regard tovisual acuity (VA) or modular transfer function (MTF)), as compared towhen there no misalignment.

Notably, the polynomial surface 2902 is uniformly arranged, in thisembodiment, over a plurality of meridians 2906 for every 0.5D(diopters). It should be appreciated that other values can be used. Insome embodiments, the polynomial surface 2902 is uniformly arranged overa plurality of meridians 2906 for every 0.41D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.42D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.44D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.46D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.45D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.48D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.52D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.54D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.56D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.58D (diopters). In someembodiments, the polynomial surface 2902 is uniformly arranged over aplurality of meridians 2906 for every 0.60D (diopters). The number ofthe added power at which the meridian are uniformly distributed is setat an individual eye's tolerance of meridian power change such as theastigmatic or cylinder power. This value changes individually, up to1.0D (diopters), but on average a comfortable tolerance is about 0.5D atthe IOL plane.

FIG. 30 is a diagram of the ETA polynomial surface 2902 of FIG. 29 shownwith the plurality of uniformly arranged meridians 206 (shown as 2906a-2906 ee), in accordance with an illustrative embodiment. As shown inFIG. 30 (and in FIG. 29), the ETA polynomial surface 2902, in thisexample, includes three regions 3002, 3004, 3006 (the center shown as3002 a, 3004 a, and 3006 a) of corrective cylindrical power—the firstregion 3002 spanning between meridians 2906 aa and 2906 dd; the secondregion 3004 spanning between meridians 2906 d and 2906 g; and the thirdregion 3006 spanning between meridians 2906 k and 2906 n. As shown, eachof the meridians (2906 a-2906 q and 2906 x-2906 a) are uniformlyarranged (i.e., uniformly spaced at various angular positions—here about11 degrees apart) for every 0.5D (diopters).

As shown in FIG. 30, meridian 2906 a is located at about 90 degrees;meridian 2906 b is located at about 79 degree; meridian 2906 c islocated at about 67 degree; meridian 2906 d is located at about 55degree; meridian 2906 e is located at about 44 degree; meridian 2906 fis located at about 33 degree; meridian 2906 g is located at about 24degree; meridian 2906 h is located at about 11 degree; meridian 2906 iis located at about 0 degree; meridian 2906 j is located at about −12degree; meridian 2906 k is located at about −24 degree; meridian 29061is located at about −36 degree; meridian 2906 m is located at about −47degree; meridian 2906 n is located at about −56 degree; meridian 2906 ois located at about −67 degree; meridian 2906 p is located at about −79degree; and meridian 2906 q is located at about −90 degree; meridian2906 r is located at about −100 degree; meridian 2906 s is located atabout −112 degree; meridian 2906 t is located at about −125 degree;meridian 2906 u is located at about −135 degree; meridian 2906 v islocated at about −145 degree; meridian 2906 w is located at about −158degree; meridian 2906 x is located at about −176 degree; meridian 2906 yis located at about 168 degree; meridian 2906 z is located at about 157degree; meridian 2906 aa is located at about 145 degree; meridian 2906bb is located at about 133 degree; meridian 2906 cc is located at about123 degree; meridian 2906 dd is located at about 113 degree; andmeridian 2906 ee is located at about 101 degree.

It is contemplated that the ETA polynomial surface 102 may include morethan three regions of corrective cylindrical power, e.g., a fourthregion, a fifth region, and etc. In such embodiments, the regionsbetween the corrective meridians may be uniformly reduced, e.g., toabout 10 degrees apart, about 9 apart, about 8 degrees apart, about 7degrees apart, and etc.

Table 1 illustrates examples of toric IOL designs with meridiansuniformly distributed for a same added power, for a 0.25D same addedpower, for a 0.5D same added power, for a same 0.75D same added power,and for a same 1.0D same added power.

TABLE 1 Number of Max meridians Added Power (in Added (from lowdiopters) between Power to low power over Max number of each meridian(diopters) ¼ of the lens) corrective regions 0.25 D 4 D 16 (4/0.25) 60.5 D 4 D 8 (4/0.5) 3 0.75 D 4 D 5.3 (4/0.75)  3 1.0 D 4 D 4 (4/1)   3

As shown in Table 1, when the meridians are uniformly arranged for asame added power of 0.5D, for a 4D base, there are 8 meridians betweenthe high power meridian and the low power meridian in a quadrant of thepolynomial surface between meridian 2906 a and 2906 i. This allows forup to 3 corrective regions on the polynomial surface, as shown in FIG.30. In another embodiment, when the meridians are uniformly arranged fora same added power of 0.75D, for a 4D base, there are 5.4 meridiansbetween the high power meridian and the lower power. This allows up to 3corrective regions of the polynomial surface. In another embodiment,when the meridians are uniformly arranged for a same added power of0.25D, for a 4D base, there are 16 meridians between the high powermeridian and the lower power. This allows up to 6 corrective regions ofthe polynomial surface. In another embodiment, when the meridians areuniformly arranged for a same added power of 1.0, for a 4D base, thereare 2 meridians between the high power meridian and the lower power.This allows up to 3 corrective regions of the polynomial surface, whichhas the high power meridian center located at meridians 2906 e, 2906 s,and 2906 cc.

FIG. 31 is a profile of the polynomial surface of FIG. 29 with theplurality of uniformly arranged meridians, in accordance with anillustrative embodiment. As shown in FIG. 31, each meridian (e.g., 2906b, 2906 c, 2906 d, 2906 e, 29060 is defined by an angular position thatis uniformly arranged, about 11 degrees apart, for every 0.5D(diopters). In addition, the majority of meridian power change, from onemeridian to the next, generates a change of more than 0.6D powerdifference (shown as 3104). The result is a profile that is moreuniformly sloped that provided extended range of operation beyond about5 degrees of misalignment (e.g., up to 10 degrees misalignment), ascompared to a conventional or macro regular cylindrical surface withpower changes according to COS(2*theta) trend, for a given differencebetween two meridians, shown as profile 3106. As shown in profile 3106,the meridian distribution is not uniform. Specifically, the meridian (indegrees) from the minimum power meridian—namely 0 degrees (3108 a)—islocated at a 20.7-degree position (3108 b), a 30-degree position (3108c), a 37.8-degree position (3108 d), a 45.0-degree position (3108 e), a52.2-degree position (31080, a 60-degree position (3108 g), a69.3-degree position (3108 h), a 90.0-degree position (3108 i), andetc., in a periodic trend, which provides a non-uniform meridiandifference of about 20.7 degrees (between 3108 a and 3108 b), about 9.3degrees (between 3108 b and 3108 c), about 7.8 degrees (between 3108 cand 3108 d), about 7.2 degrees (between 3108 d and 3108 e), about 7.2degrees (between 3108 e and 31080, about 7.8 degree (between 3108 f and3108 g), about 9.3 (between 3108 g and 3108 h), and about 20.7 degree(between 3108 h and 3108 i).

Referring still to FIG. 31, off-center structures of the polynomialsurface 2902 extend from the center structure in a gradually varyingmanner to apply cylinder power to a band of meridians surrounding thecorrective meridian enabling the ophthalmic apparatus to operateoff-axis (or off-meridian) to the corrective meridian (e.g., theastigmatism meridian). Notably, there are no more than 0.6-Diopterdifference between any neighboring uniformly distributed contour lines.

In some embodiments, the polynomial surface 2902 is defined by acombination of spline or polynomial (e.g., a Zernike polynomial, aChebyshev polynomial, or a combination of both) that is constrained bythe condition of the meridians being uniformly arranged apart for a samegiven added diopter of power up to 1.0D (diopters).

FIG. 32 illustrates an example operation of the polynomial surface 2902of FIG. 29 when subjected to misalignment, in accordance with anillustrative embodiment. The polynomial surface 2902, as a diffractiveor refractive structure, in some embodiments, varies the extended depthof focus to a plurality of nearby focus points. To this end, lightdirected to such nearby focus points are thus directed to the desiredfocus point when the ophthalmic apparatus is subjected to a rotationaloffset from a primary intended axis of alignment, thereby extending therotational tolerance of the apparatus to an extended tolerance band. InFIG. 32, a portion (3202) of the polynomial surface 2902 has a focuspoint 3204 (e.g., referred to as a “main focus point” 3204, e.g., tocorrect for an astigmatism) that is generated by a region about thecenter 3206 of the portion 3202 of the polynomial surface 2902. In thisexample, a nearby region 3208 of that portion 3202 has a focus point3210 (e.g., referred to as an “auxiliary focus point” 3210) that isoffset from the main focus point 3204. When the polynomial surface 2902is rotated about axis 2912, e.g., as misalignment 2906 is introduced tothe corrective meridian Θ=0° (2904), the focus point 3210 of region 3208is moved towards the main focus point 3204, thereby extending the bandof operation of the polynomial surface 2902. Remarkably, this extendedtolerance astigmatism band delivers cylinder power to correct for theastigmatism for a range of meridians (e.g., up to ±10° as shown in FIG.29, though can be more in other embodiments), thereby eliminating anyneed for additional corrective measures (e.g., supplemental correctivedevices or another surgical intervention) when the implanted ophthalmicapparatus is not perfectly aligned to the desired astigmatism meridianin the eye.

Put another way, the polynomial surface 2902 facilitates an extendedband of the corrective meridian that has minimal, and/or clinicallyacceptable, degradation of the visual acuity and modulation transferfunction when the ophthalmic apparatus is subjected to rotationalmisalignment between the astigmatic axis and a center axis of thecorrective meridian.

Results of IOL with Exemplified Freeform-Polynomial Surfaces

FIG. 33 shows a combined cylinder map generated from the combination ofthe IOL cylindrical power (provided, in part, via the polynomialsurface) combined with the corneal cylindrical power through meridians.FIG. 34 shows the combined cylinder map of FIG. 33 with the meridiansshown in FIG. 30 superimposed thereon.

As discussed above with reference to FIG. 29, and as can be seen fromthe IOL cylinder map through meridians around the clock, there isremarkably no more than about 0.6D difference for any continuousuniformly distributed contour lines at the IOL plane. The IOL SE is 20Dat the IOL plane. The IOL cylinder map of FIG. 29 is combined with theIOL SE to provide the overall IOL cylindrical map. That is, theastigmatism associated with test corneal cylindrical power has beenattenuated and/or corrected for by the IOL cylindrical power provided,in part, by the polynomial surface.

FIGS. 35A and 35B each shows calculated MTF values as spatialfrequencies of an exemplified IOL 100 in a physiological eye model withastigmatic cornea in different cylindrical axis misalignment (CAM)situations between the cornea and the IOL for an iris pupil. Notably, asshown in FIGS. 35A and 35B, the modulation transfer function (MTF) ismaintained across the extended range of alignment for a lens configuredwith the freeform-polynomial surface area 2902 of FIG. 29. Specifically,in FIGS. 35A and 35B, the MTFs for misalignment at 0 degrees, 5 degrees,and 10 degrees are shown (shown as “CAM=0 Deg” 3502, “CAM=5 Deg” 3504,and “CAM=10 Deg” 3506). In FIG. 35A, the iris pupil is about 3.0 mm. InFIG. 35B, the iris pupil is about 5.0 mm.

Notably, as can also be seen from the MTF curves, there are no cut-offsof the spatial frequency beyond 100 cpd (cycles per degree), which foran IOL with SE (Spherical Equivalent) of 20D (Diopters), this spatialfrequency is approximately 30 cpd.

Corneal Irregular Geometry or Limited Retinal Area Functions

In another aspect, the polynomial surface 2902 of FIG. 29 is optimizedto purposely place accumulated high surface amplitude (also referred tohigh order aberration) to non-functional retinal area so that thefunctional areas can fully benefit the ETA designs, that is, theenhanced image quality stability. Examples of non-functional retinalareas may include, but not limited to, areas of gradual loss of sight(e.g., associated with glaucoma or retinal macular degeneration (AMD).

Referring to FIG. 30, an accumulated high surface amplitude results atarea 3008 to provide enhanced image quality stability for the threecorrective regions 3002, 3004, 3006 that have uniform distributionsdiscussed herein. In some embodiments, the corrective regions (e.g.,3002, 3004, 3006) effectively span over a region greater than 90 degreesto angular extent. Confined by a finite surface region, it iscontemplated that the accumulated (high) surface amplitude area 3008 ispurposely positioned (in a manner similar to the positioning of thecorrective regions 3002, 3004, 3006) to coincide, e.g., with areas oflimited retinal functionality that may be present with a given patient.That is, the accumulated (high) surface area is specifically optimizedoptically to target the special optical needs of the entire eye on thisarea.

FIG. 36 is a surface SAG map of the polynomial surface 2902 of FIG. 29,in accordance with an illustrative embodiment.

Referring back to FIG. 23, the diagram also shows a method to generate,via a processor, the polynomial surface of FIG. 29, in accordance withan illustrative embodiment. As shown in FIG. 23, the method includesgenerating (2302), via a processor, an initial freeform polynomialdesign (2304) comprising a base surface (with base cylindrical power)and sectional enhancements (with added cylindrical power in which eachmeridian is uniformly arranged for a same given added power) anditeratively generating (2306) and evaluating, a revised freeformpolynomial design (1310), generated according to an optimization routine(2308) that is performed based on sectional parameters, untilpre-defined image quality metric values and boundary parameter areachieved. The sectional enhancements power of the initial freeformpolynomic design and the iterative freeform polynomic design are the ETApolynomial surface of FIG. 29.

The section surface optical parameters 1314 of the freeform polynomialsurface, in some embodiments, includes parameters associated withsectional added power and meridian characteristics (shown as “Sectionaladd power” 1328) and parameters associated with high order aberrationcharacteristics, e.g., Zernike aberrations above second-order (shown as“High order aberrations” 1328).

Referring still to FIG. 23, the parameters associated with the sectionaladded power 1326, in some embodiments, include a cylindrical power, fora given optical zone, for a same given added power in which meridiansare uniformly arranged. In some embodiments, the cylindrical power forthe added power are all refractive. The parameters associated with thehigh order aberration characteristics 1328, in some embodiments, includepolynomial values (e.g., based on Zernike polynomials, Chebyshevpolynomials, and combinations thereof) or characteristics such aspolynomial orders and types as well as meridian boundaries for the highorder aberrations. The high order aberration is constrained, e.g., fromminimum to maximum cylindrical power over one or more meridian sections.In some embodiments, the high order aberrations is constrained ordesignated to a meridian, e.g., that corresponds to a corneal irregulargeometry or limited retinal area functions. In such embodiments, thehigh order aberrations and its meridian locations on the lens surfacemay be optimized prior to the meridians for the uniform regions aredetermined to facilitate a customized design that is tailored for agiven patient (i.e., particularly in view of corneal irregular geometryor limited retinal area functions). Such customization has a potentialto truly benefit patients having cornea with or without astigmatism,patients with local Keratoconus with or without astigmatism, patientswith glaucoma, patients with retinal macular degeneration (AMD), and thelike.

Referring still to FIG. 23, the parameters associated with thepre-defined image quality metric value 1316 includes parametersassociated with expected image quality metric (shown as “Expected imagequality metric values” 1330) and parameters associated with specialboundary restrain parameters (shown as “Special boundary restrainparameters” 1332). In some embodiments, image quality metric is based acomparison of a base polychromatic diffraction MTF (modular transferfunction) (e.g., tangential and sagittal) to a number of errorpolychromatic diffraction MTFs values, e.g., where one or morepolychromatic diffraction MTFs are determined for one or moremisalignments of the generated toric lens from its intended operatingmeridians, e.g., at 5-degree misalignment and at 10-degree misalignment.

Referring still to FIG. 23, the initial design (1304) is evaluated (1334a) to determine image quality metric values (e.g., the basepolychromatic diffraction MTF, e.g., at 0 degree misalignment) and theerror polychromatic diffraction MTFs, e.g., at the 5 and 10 degreesmisalignment) and boundary parameters, e.g., as shown in FIGS. 35A and35B. The determined image quality metric values are evaluated (1336) todetermine whether the image quality metric values and boundaryparameters meet an expected outcome, e.g., a value of 0.2. In someembodiments, the expected outcome is whether there is no cut off throughspatial frequency beyond 100 cpd. Upon determining that the condition ismet, the method 1300 is stop (1338). It is contemplated that other imagequality metrics may be used, e.g., the optical transfer function (OTF),phase transfer function (PhTF), and etc.

Where the condition is not met, the method 1300 adjusts (1308) sectionalparameters to be optimized and rerun the optimization to generate therevised design 1310. The adjusted sectional parameters may includemeridians locations and meridian spacing among neighboring meridians.The optimization may include allowing the uniform contour lines to movefrom one meridian to a next meridian up based on an upper limit amountand a lower limit amount. As shown in FIG. 30, the uniform contour line3010 is show transitioning from meridian 2906 m to meridian 2906 n. Thetransition is constrained to occur along a specific radial position andwithout abrupt transition points.

Referring back to FIG. 23, the method 300 then includes evaluating (2334b) the revised design 2310 to determine image quality metric values(e.g., the base polychromatic diffraction MTF, e.g., at 0 degreemisalignment) and the error polychromatic diffraction MTFs, e.g., at the5 and 10 degrees misalignment) and boundary parameters, as discussed inrelation to step 2334 a, and re-evaluating (2336) whether the revisedimage quality metric values and boundary parameters meet the expectedoutcome, as discussed in relation to step 2336.

The present technology may be used, for example, in the Tecnis toricintraocular lens product line as manufactured by Abbott Medical Optics,Inc. (Santa Ana, Calif.).

It is not the intention to limit the disclosure to embodiments disclosedherein. Other embodiments may be used that are within the scope andspirit of the disclosure. In some embodiments, the above disclosedangularly varying phase members may be used for multifocal toric,extended range toric, and other categorized IOLs for extended toleranceof astigmatism caused by factors including the cylindrical axismisalignment. In addition, the above disclosed angularly varying phasemembers may be applied to spectacle, contact lens, corneal inlay,anterior chamber IOL, or any other visual device or system.

Exemplary Computer System

FIG. 37 is a diagram of an example computing device configured togenerate the surface with the angularly-varying phase members. As usedherein, “computer” may include a plurality of computers. The computersmay include one or more hardware components such as, for example, aprocessor 3721, a random access memory (RAM) module 3722, a read-onlymemory (ROM) module 3723, a storage 3724, a database 3725, one or moreinput/output (I/O) devices 3726, and an interface 3727. Alternativelyand/or additionally, controller 3720 may include one or more softwarecomponents such as, for example, a computer-readable medium includingcomputer executable instructions for performing a method associated withthe exemplary embodiments. It is contemplated that one or more of thehardware components listed above may be implemented using software. Forexample, storage 3724 may include a software partition associated withone or more other hardware components. It is understood that thecomponents listed above are exemplary only and not intended to belimiting.

Processor 3721 may include one or more processors, each configured toexecute instructions and process data to perform one or more functionsassociated with a computer for indexing images. Processor 3721 may becommunicatively coupled to RAM 3722, ROM 3723, storage 3724, database3725, I/O devices 3726, and interface 3727. Processor 3721 may beconfigured to execute sequences of computer program instructions toperform various processes. The computer program instructions may beloaded into RAM 3722 for execution by processor 3721. As used herein,processor refers to a physical hardware device that executes encodedinstructions for performing functions on inputs and creating outputs.

RAM 3722 and ROM 3723 may each include one or more devices for storinginformation associated with operation of processor 3721. For example,ROM 3723 may include a memory device configured to access and storeinformation associated with controller 3720, including informationassociated with IOL lenses and their parameters. RAM 3722 may include amemory device for storing data associated with one or more operations ofprocessor 3721. For example, ROM 3723 may load instructions into RAM3722 for execution by processor 3721.

Storage 3724 may include any type of mass storage device configured tostore information that processor 3721 may need to perform processesconsistent with the disclosed embodiments. For example, storage 3724 mayinclude one or more magnetic and/or optical disk devices, such as harddrives, CD-ROMs, DVD-ROMs, or any other type of mass media device.

Database 3725 may include one or more software and/or hardwarecomponents that cooperate to store, organize, sort, filter, and/orarrange data used by controller 3720 and/or processor 3721. For example,database 3725 may store hardware and/or software configuration dataassociated with input-output hardware devices and controllers, asdescribed herein. It is contemplated that database 3725 may storeadditional and/or different information than that listed above.

I/O devices 3726 may include one or more components configured tocommunicate information with a user associated with controller 3720. Forexample, I/O devices may include a console with an integrated keyboardand mouse to allow a user to maintain a database of images, updateassociations, and access digital content. I/O devices 3726 may alsoinclude a display including a graphical user interface (GUI) foroutputting information on a monitor. I/O devices 3726 may also includeperipheral devices such as, for example, a printer for printinginformation associated with controller 3720, a user-accessible diskdrive (e.g., a USB port, a floppy, CD-ROM, or DVD-ROM drive, etc.) toallow a user to input data stored on a portable media device, amicrophone, a speaker system, or any other suitable type of interfacedevice.

Interface 3727 may include one or more components configured to transmitand receive data via a communication network, such as the Internet, alocal area network, a workstation peer-to-peer network, a direct linknetwork, a wireless network, or any other suitable communicationplatform. For example, interface 3727 may include one or moremodulators, demodulators, multiplexers, demultiplexers, networkcommunication devices, wireless devices, antennas, modems, and any othertype of device configured to enable data communication via acommunication network.

While the methods and systems have been described in connection withpreferred embodiments and specific examples, it is not intended that thescope be limited to the particular embodiments set forth, as theembodiments herein are intended in all respects to be illustrativerather than restrictive.

Unless otherwise expressly stated, it is in no way intended that anymethod set forth herein be construed as requiring that its steps beperformed in a specific order. Accordingly, where a method claim doesnot actually recite an order to be followed by its steps or it is nototherwise specifically stated in the claims or descriptions that thesteps are to be limited to a specific order, it is no way intended thatan order be inferred, in any respect. This holds for any possiblenon-express basis for interpretation, including: matters of logic withrespect to arrangement of steps or operational flow; plain meaningderived from grammatical organization or punctuation; the number or typeof embodiments described in the specification.

What is claimed is:
 1. A rotationally-tolerant intraocular lens (IOL),the intraocular lens comprising a multi-zonal optic body comprising oneor more angularly-varying phase members that each includes an optimizedcombination of angularly and zonally diffractive phase structure locatedacross one or more optical zones to apply power at one or morecorrecting meridian, wherein each of the one or more angularly-varyingphase members applies the power at a given correcting meridian and varyan extended depth of focus to a plurality of nearby points of focus toprovide an extended tolerance to misalignment of the intraocular lenswhen implanted in an eye, the multi-zonal optic body forming a firstangularly-varying phase member having a peak cylinder power centered ata first correcting meridian, the first angularly-varying phase member atthe peak cylinder power being configured to direct light, at the firstcorrecting meridian, to a first point of focus on the retina, wherein atangular positions nearby to the first correcting meridian, theangularly-varying phase member varies, at each optical zone, and isconfigured to direct light to points of focus nearby to the first pointof focus such that the multi-zonal optic body, when rotational offsetfrom the peak cylinder power, directs light from the nearby points offocus to the first point of focus, thereby establishing an extended bandof operational meridians over the first correcting meridian, whereineach phase structure has a height profile at a face of the multi-zonaloptic body that varies along the extended band of operational meridiansover each respective corrective meridian.
 2. The intraocular lens ofclaim 1, wherein the multi-zonal lens body forms the angularly-varyingphase member, wherein a height profile T1(r, θ) for each meridian θ isdefined as:T1(r,θ)=t ₁(r)|COS²(θ)|+t ₂(r)|SIN²(θ)| where t₁(r) and t₂(r) are theadded power for each zone.
 3. The intraocular lens of claim 2, whereinthe multi-zonal lens body comprises at least four optical zones, the atleast four optical zones forming an angularly varying efficiency quadricoptics.
 4. The intraocular lens of claim 3, wherein theangularly-varying phase members, collectively, form a pattern that isexpressed as${{r(\theta)} = \sqrt{2 \cdot n \cdot \frac{{s(\theta)} \cdot \lambda}{A(\theta)}}},$where r(θ) is the contour radius for the given meridian added powerA(θ), wavelength λ, zone number n, and the scaling value s(θ), all atmeridian θ.
 5. The intraocular lens of claim 1, wherein theangularly-varying phase member spans an optical zone defined by apolynomial-based surface coincident at a plurality of meridians havingdistinct cylinder powers, wherein each of the plurality of meridians isuniformly arranged on the optical zone for a same given added diopter ofpower up to 1.0D.
 6. The intraocular lens of claim 5, whereindifferences among each continuously uniformly distributed contour line,at a given IOL plane, associated with a given meridian of the pluralityof meridians is less than about 0.6D (diopters).
 7. The intraocular lensof claim 5, wherein the polynomial-based surface is characterized by aseries of weighted cosine-based functions.
 8. The intraocular lens ofclaim 1, wherein the one or more angularly-varying phase members eachspans a first optical zone defined by a freeform-polynomial surface areacoincident with one or more distinct cylinder powers, wherein thefreeform-polynomial surface area is defined as a mathematical expressioncomprising a combination of one or more polynomial expressions eachhaving a distinct complex orders.
 9. The intraocular lens of claim 8,wherein at least one of the one or more polynomial expressions areselected from the group consisting of a Chebyshev polynomial and aZernike polynomial.
 10. The intraocular lens of claim 8, wherein thefreeform-polynomial surface area establishes the extended band ofoperational meridian across a range selected from the group consistingof about ±4 degrees, about ±5 degrees, about ±6 degrees, about ±7degrees, about ±8 degrees, about ±9 degrees, about ±10 degrees, about±11 degrees, about ±12 degrees, about ±13, degrees, about ±14 degrees,and about ±15 degrees.
 11. The intraocular lens of claim 8, wherein thefreeform-polynomial surface area has a second height profile T(x,y) on afirst base height profile, the second height profile being defined as:T(x,y)=Σ{c(i,j)*cos(i*arccos(t))*cos(j*arccos(t))} where c(i, j) is acoefficient based on i and j, which are each integers, x and y arespatial locations on the freeform-polynomial surface area, and t is anormalized parameter having values between −1.0 and 1.0.
 12. Theintraocular lens of claim 11, wherein the coefficients c(i,j) or c₂(i₂,j₂) are a function of local coordinates that puts accumulated highsurface amplitude to area of non-functional retinal area.
 13. Theintraocular lens of claim 11, wherein the coefficients c(i,j) or c₂(i₂,j₂) are a function of local coordinates that accounts for irregularcorneal shape.
 14. The intraocular lens of claim 8, wherein the one ormore optical zones includes the first optical zone and a second opticalzone, wherein the second optical zone is defined by a secondfreeform-polynomial surface region characterized and defined by a secondpolynomial, wherein the second freeform-polynomial surface area has athird height profile T₂(x,y) superimposed on a first height profile(e.g. a base or typical aspheric height profile), the third heightprofile being defined as:T ₂(x,y)=Σ{c ₂(i ₂ ,j ₂)*cos(i ₂*arccos(t ₂))*cos(j ₂*arccos(t ₂))}where c₂(i, j) is a coefficient based on i₂ and j₂, which are eachintegers, x and y are spatial locations on the secondfreeform-polynomial surface area and has values between −1.0 and 1.0,and t₂ is a normalized parameter having values between −1.0 and 1.0. 15.The intraocular lens of claim 14, wherein the first freeform-polynomialsurface area and the second freeform-polynomial surface area eachcomprises a monofocal lens, a bifocal lens, a multi-focal lens, or anextended range of vision lens.
 16. The intraocular lens of claim 1,wherein the angularly-varying phase member is formed of a refractivestructure.
 17. The intraocular lens of claim 1, wherein theangularly-varying phase member is formed of a diffractive structure. 18.The intraocular lens of claim 1, wherein an offset of each meridian ofthe plurality of meridians of about 10 degrees causes a MTF (modulationtransfer function) measure change of less than 10% at 30 cycles perdegree (cpd).
 19. The intraocular lens of claim 1, wherein themulti-zonal optic body forms a a second angularly-varying phase memberhaving a second peak cylindrical power centered at a second correctingmeridian, the second angularly-varying phase member at the second peakcylinder power being configured to direct light to a second point offocus on the retina, wherein at angular positions nearby to the firstmeridian, wherein the second angularly-varying phase member varies alongmeridian nearby to the second point of focus such that the multi-zonaloptic body, when rotational offset from the second peak cylinder power,directs light from the nearby points of focus to the second point offocus.
 20. The intraocular lens of claim 1, wherein the intraocular lenscomprises an intraocular toric lens.